System and sensor array

ABSTRACT

The present disclosure provides a system comprising a communication interface and computer for assigning a label to the biomolecule fingerprint, wherein the label corresponds to a biological state. The present disclosure also provides a sensor arrays for detecting biomolecules and methods of use. In some embodiments, the sensor arrays are capable of determining a disease state in a subject.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. application Ser. No. 17/901,294, filed Sep. 1, 2022, which is a continuation of U.S. application Ser. No. 17/215,923 filed Mar. 29, 2021 now patented as U.S. Pat. No. 11,435,360, which is a division of U.S. application Ser. No. 17/099,331 filed Nov. 16, 2020; which is a continuation-in-part of U.S. application Ser. No. 15/880,627 filed Jan. 26, 2018 now patented as Pat. No. 10,866,242; which is a continuation of International Application PCT/US2017/067013 filed on Dec. 18, 2017 which claims priority to U.S. Provisional Application 62/435,409 filed Dec. 16, 2016, the contents of which are incorporated by reference in its entirety.

STATEMENT REGARDING FEDERALLY SPONSORED RESEARCH

N/A

INCORPORATION BY REFERENCE

All publications, patents, and patent applications mentioned in this specification are herein incorporated by reference to the same extent as if each individual publication, patent, or patent application was specifically and individually indicated to be incorporated by reference.

BACKGROUND OF THE INVENTION

The field of the invention is related to sensor arrays for the detection and diagnosis of different disease states, particularly, the invention relates to the ability to diagnose or prognose diseases or disorders.

The earlier a disease is diagnosed, the more likely that the disease can be cured or successfully managed leading to a better prognosis for the patient. When you treat a disease early, you may be able to prevent or delay problems from the disease and may improve the outcomes for the patient, including extending the patient's life and/or quality of life.

Early diagnosis of cancer is crucial, as many types of cancers can be successfully treated in their early stages. For example, five-year survival after early diagnosis and treatment of breast, ovarian, and lung cancers is 90%, 90%, and 70%, respectively, compared to 15%, 5%, and 10% for patients diagnosed at the most advanced stage of disease. Once cancer cells leave their tissue of origin, successful treatment using available established therapeutics becomes very unlikely. Although recognizing the warning signs of cancers and taking prompt action may lead to early diagnosis, the majority of cancers (e.g., lung) show symptoms only after cancer cells have already invaded the surrounding tissues and metastasized throughout the body. For example, more than 60% of patients with breast, lung, colon, and ovarian cancer have concealed or even metastatic colonies by the time their cancers are detected. Therefore, there is an urgent need for development of an effective approach for early detection of cancer. Such an approach should have the sensitivity to identify a cancer at various stages and the specificity to give a negative result when the person being tested is free of the cancer. There have been extensive efforts to develop methods for early detection of cancers; although huge numbers of risk factors and biomarkers have been introduced, a broadly relevant platform for early detection of a wide range of cancers remains elusive.

As various types of cancers can change the composition of blood plasma—even in their early stages—one promising approach for early detection is molecular blood analysis for biomarkers. Although this strategy has already worked for a few cancers (like PSA for prostate cancer), there are not yet specific biomarkers for early detection of the majority of cancers. For such cancers (e.g., lung), none of the defined candidate circulating biomarkers has been clinically validated, and very few have reached late-stage clinical development. Therefore, there is an urgent need for novel approaches to improve our ability to detect cancer at very early stages.

SUMMARY OF THE INVENTION

The present invention provides a sensitive versatile sensor array for detection of a wide range of diseases and disorders and determination of disease states in a subject. The uniqueness of the present invention is the combination of this recognition of a biomolecular fingerprint from a sample from a subject and the ability to determine a disease state for that subject on a continuum of health.

In some aspect, the invention provides a sensor array comprising a plurality of sensor elements, wherein the plurality of sensor elements differ from each other in at least one physicochemical property and the plurality of sensor elements comprises at least two sensor elements. In some aspects, each sensor element is able to bind a plurality of biomolecules in a sample to produce a biomolecule corona signature, wherein each sensor element has a distinct biomolecule corona signature from the other. In some aspects, the sensor element is a nanoscale sensor element.

In some aspects, the plurality of sensor elements produces a plurality of biomolecule corona signatures when contacted by the sample, wherein the combination of the plurality of biomolecule corona signatures produces a biomolecule fingerprint for the sample.

In some aspects, the sensor elements are linked to the substrate.

In some aspects, the sensor elements are discrete elements (regions) on a substrate, plate or chip having topological and functional differences where each distinct element (region) produces a distinct biomolecule corona signature. Together, the substrate, chip or array itself forms the sensor array and provide the biomolecule fingerprint for the sample.

In some aspects, the invention provides methods of detecting a disease state in a subject comprising: obtaining a sample from the subject; contacting the sample with a sensor array, wherein the sensor array comprises a plurality of sensor elements, wherein the plurality of sensor elements differ from each other in at least one physicochemical property and the plurality of sensor elements comprises at least two sensor elements, and determining a biomolecule fingerprint associated with the sample, wherein the biomolecule fingerprint may differentiate the disease state of the subject. In some aspects, the method further comprises comparing the biomolecule fingerprint of the sample to a panel of biomolecule fingerprints associated with a plurality of disease states to determine which disease state is associated with the sample.

In another aspect, the invention provides a method of determining a biomolecule fingerprint associated with at least disease state or at least one disease or a disorder, the method comprising the steps of: (a) obtaining a samples from at least two subjects diagnosed with the disease state or the at least one disease or disorder; (b) contacting each sample with a sensor array described herein, and (c) determining a biomolecule fingerprint for the sensor array that is associated with the disease state or at least one disease or disorder. In some aspects, step (c) further comprises detecting the composition of the biomolecule corona of each sensor element, wherein the combination of the composition of each biomolecule corona between the different sensor elements produce the biomolecule fingerprint associated with the sample. In other aspects, step (c) comprises dissociating the biomolecule corona from each sensor element and assaying the plurality of biomolecules of each biomolecule corona, wherein the combination of biomolecules assayed produced the biomolecule fingerprint.

In yet another aspect, the invention provides a method of diagnosing or prognosing a disease or disorder in a subject, comprising obtaining a sample from a subject; contacting the sample with a sensor array described herein to produce a biomolecule fingerprint, comparing the biomolecule fingerprint to a panel of biomolecule fingerprints associated with a plurality of diseases or disorders; and diagnosing or prognosing the disease or disorder.

In yet another aspect, the invention provides a method of identifying a pattern of biomarkers associated with a disease or disorder, the method comprising: (a) obtaining a samples from at least two subjects diagnosed with the disease or disorder and at least two control subjects; (b) contacting each sample with a sensor array to produce a plurality of biomolecule corona for each subject, and (c) comparing the composition of the plurality of biomolecule corona of the subjects with the disease or disorder to the composition of the plurality of biomolecule corona of the control subjects to determine a pattern of biomarkers associated with the disease or disorder.

In some aspects, the disease or disorder is cancer, endocrine disorder, cardiovascular disease, inflammatory disease or a neurological disease.

In one aspect, the disease or disorder is cancer.

In another aspect, the disease or disorder is cardiovascular disease. In one aspect, the cardiovascular disease is coronary artery disease (CAD).

In a further aspect, the disease or disorder is a neurological disorder. In one aspect, the neurological disorder is Alzheimer's disease.

In some aspects, the invention provides a kit for diagnosing or prognosing a disease or disorder, the kit comprising: a sensor array comprising a plurality of nanoscale sensor elements, wherein the plurality of sensor elements differ from each other in at least one physicochemical property and the plurality of sensor elements comprises at least two sensor elements.

In other aspects, the invention provides kit for determining and/or detecting at least one biomarker associated with a disease or disorder, comprising at least one sensor array comprising a plurality of sensor elements, wherein the plurality of sensor elements differ from each other in at least one physicochemical property and the plurality of sensor elements comprises at least two sensor elements.

In yet another aspect, the invention provides a method of distinguishing states of a complex biological sample of a subject using a plurality of particles having surfaces with different physicochemical properties, wherein the method comprises: exposing the complex biological sample to the plurality of particles to permit binding of proteins of the complex biological sample to the plurality of particles, wherein a pattern of binding of proteins amongst the plurality of particles differs based on the physicochemical properties of the surfaces of the particles; defining a biomolecule fingerprint representative of proteins that bind to the plurality of particles; and associating the biomolecule fingerprint with a biological state of the subject.

In another aspect, the invention provides a sensor array comprising a plurality of particles having surfaces with different physicochemical properties, wherein proteins of a complex biological sample bind to the plurality of particles upon exposure of the complex biological sample to the plurality of particles, wherein a pattern of binding of the proteins amongst the plurality of particles depends on the physicochemical property of a surface of the particle.

In yet a further aspect, the invention provides a sensor array comprising a plurality of liposomes, wherein the plurality of liposomes differ in at least one protein-binding property defined by a lipid-based surface of each liposome; wherein the lipid-based surface of each liposome contacts a subset of proteins of a sample at a lipid-protein interface, thereby binding the subset of proteins to produce a pattern of protein binding; wherein the pattern of protein binding of a first liposome is different than the pattern of protein binding of a second liposome differing from the first liposome in said at least one protein-binding property.

In another aspect, the invention provides a method of identifying a biological state of a subject using a plurality of liposomes differing in at least one protein-binding property defined by a lipid-based surface of each liposome, wherein the method comprises: exposing the sample to the plurality of liposomes to permit binding of proteins of the sample to the plurality of liposomes, wherein a pattern of binding of the proteins differs amongst liposomes with different protein-binding properties; separating the proteins from the liposomes; defining a biomolecule fingerprint of the proteins separated from the liposomes; and associating the biomolecule fingerprint with a state of the complex biological sample of the subject.

The foregoing and other aspects and advantages of the invention will appear from the following description. In the description, reference is made to the accompanying drawings which form a part hereof, and in which there is shown by way of illustration a preferred embodiment of the invention. Such embodiment does not necessarily represent the full scope of the invention, however, and reference is made therefore to the claims and herein for interpreting the scope of the invention.

BRIEF DESCRIPTION OF THE DRAWINGS

The patent or application file contains at least one drawing executed in color. Copies of this patent or patent application publication with color drawing(s) will be provided by the Office upon request and payment of the necessary fee.

FIG. 1 . Scheme of one embodiment showing an example of study design of the protein corona pattern approach for cancer detection. Three types of liposomes are incubated with plasma of healthy people and cancer patients, and the protein corona pattern forming on each liposome in each subject's plasma (healthy and different cancers) is characterized by liquid chromatography-tandem mass spectrometry (LC-MS/MS). The formation of protein coronas on the three liposomes results in the enrichment of an overlapping but distinct pool of selected plasma proteins, and the enriched proteins are the bases for subsequent multivariate analysis. Via classification approaches, the important proteins in the corona patterns were identified and used to predict cancers using both blind plasmas and cohort samples to test the accuracy of the multi-nanoparticle protein corona nanosystem. 29 human subjects (25 cancerous patients, i.e., 5 patients per 5 cancer types; and 4 healthy subjects) representing 261 distinct runs of LC-MS/MS (3 liposomes, 29 subjects, 3 replicates) were used to train a classification model. 16 human subjects (3 patients per 5 cancer types; and 1 healthy subject) of blind plasma and 144 distinct runs of LC-MS/MS (3 liposomes, 16 subjects, 3 replicates) were used for cancer prediction, i.e., to test the classification model. 15 human subjects (5 patients per 3 cancer types) of cohort plasma representing 135 distinct runs of LC-MS/MS (3 liposomes, 15 subjects, 3 replicates) were used for very early cancer prediction as well.

FIG. 2A. TEM images of liposomes with their size distribution profiles.

FIG. 2B. Physicochemical properties of different liposomes before and after interactions with human plasma from patients with different diseases. DLS and Zeta-Potential data on various liposomes before interactions with human plasma and corona complexes free from excess plasma, obtained following incubation with plasma from healthy and cancer patients (Pdi: Polydispersity index from cumulant fitting).

FIG. 2C. Classification of the identified corona proteins from liposomes according to their physiological functions in human plasma of healthy individuals and of patients having different types of cancers (the data presented reflect a calculation from five biological plasmas per group and three technical replicates per plasma)

FIG. 3A. Classification of identified coronas by sensor array elements according to their physiological functions including acute phase, in human plasma of healthy subjects and patients having different types of cancers.

FIG. 3B. Classification of identified coronas by sensor array elements according to their physiological functions, including coagulation in human plasma of healthy subjects and patients having different types of cancers.

FIG. 3C. Classification of identified coronas by sensor array elements according to their physiological functions, including immunoglobulins in human plasma of healthy subjects and patients having different types of cancers.

FIG. 3D. Classification of identified coronas by sensor array elements according to their physiological functions, including lipoproteins in human plasma of healthy subjects and patients having different types of cancers.

FIG. 3E. Classification of identified coronas by sensor array elements according to their physiological functions, including tissue leakage in human plasma of healthy subjects and patients having different types of cancers.

FIG. 3F. Classification of identified coronas by sensor array elements according to their physiological functions, including complement proteins in human plasma of healthy subjects and patients having different types of cancers.

FIG. 3G. Classification of identified coronas by sensor array elements according to their physiological functions, including other plasma proteins in human plasma of healthy subjects and patients having different types of cancers.

FIG. 4A. Predictor discovery and contribution from each individual predictor to separation of each class by PLS discrimination analysis. Predictor exploration by weighted VIP was performed by adding the ranked variables to the PLS-DA model one by one and calculating the classification error for internal cross-validation (10-fold). Decreasing the classification error led to the discovery of a minimal set of 69 predictors with the highest possible importance for separating each class from the others. The contribution of each individual marker to separation of each class based on the PLS discrimination analysis. VIP plot ranking markers of 69 selected variables for their contribution to separation of each class from PLS discrimination analysis. VIP score >1 indicates important protein leading to good prediction of class membership, whereas variables with VIP scores <1 indicate unimportant proteins for each class.

FIG. 4B depicts the results for the 69 variables for glioblastoma.

FIG. 4C. Depicts the VIP values for the 69 variables for meningioma.

FIG. 4D. Depicts the VIP values for the 69 variables for lung cancer.

FIG. 4E. Depicts the VIP values for the 69 variables for myeloma.

FIG. 4F. Depicts the VIP Values for the 69 variables for pancreatic cancer.

FIG. 5A. PLS-DA plot showing the separation of different cancerous samples from each other and from controls. PLS score-plot obtained using PLS-toolbox, projecting the objects into the subspace created by the 1st, 2nd, and 3rd latent variables of the model.

FIG. 5B. PLS-DA plot showing the separation of different cancerous samples from each other and from controls. Objects displayed where the 4th and 5th latent variables of the model are shown. As can be seen, meningioma and glioblastoma cases were not separated in three dimensions appropriately, but they can be separated in the fourth and fifth dimensions of the PLS model.

FIG. 5C. Assignation map obtained by CPANN with all variables and selected variables. The assignation map obtained by training of a CPANN network (8×8 neurons) using whole data set (1823 variables). The mapping quality is not good and there are conflicts of different types of cancer in term of mapping.

FIG. 5D. Assignation map attained by training of a CPANN network (8×8 neurons) using 69 variables. High dimensional input vectors (samples) are mapped on a two-dimensional network of neurons, preserving similarity and topology. Colors indicate the similarity of a neuron to a specific type of input vector (class type). This map also demonstrates the importance of the predictor selection step and the effect of deletion of non-informative and irrelevant predictors on the model quality.

FIG. 5E. Dendrogram depicting the 51 proteins identified as capable of distinguishing among the six groups of cancer.

FIG. 5F. The 51 proteins identified as capable of distinguishing among the six groups are presented in a ‘Heat Map’ generated with an unsupervised cluster algorithm (Agglomerative HCA with furthest neighbor linkage). Visual inspection of both the dendrogram (FIG. 5E) and heat map (FIG. 5F) demonstrates cancer-specific protein corona signature and clear clustering of six groups of samples (five groups of cancerous samples plus normal samples) and also expected similarities among five patients from each group. The heat map also indicates substantial differences in the patterns of variables (markers) of different cancers (each column represents a patient, and each row represents a protein). Higher and lower protein levels are indicated in red and green, respectively.

FIG. 6A. PLS score-plot obtained by considering 69 important markers, projecting the cohort objects into the subspace created by the 1st and 2nd latent variables of the model.

FIG. 6B. PLS-DA Model is generated using 8 variables projecting the cohort objects into the subspace created by the 1st and 2nd latent variables of the model, with excellent statistics.

FIG. 6C. The assignation map obtained by training of a CPANN network (8×8 neurons) using 69 important markers.

FIG. 6D. The assignation map obtained by training of a CPANN network (8×8 neurons) using only 8 markers without any misclassifications. Sample numbers are indicated on each neuron.

FIG. 7A. Schematic representation of study outline. Informative variable selection and classification model building.

FIG. 7B. The protein name and ID of 69 selected variables are listed. Some of the proteins were present in the protein corona of more than one liposome (DOPG, DOTAP and CHOL are denoted by fonts: Italic and underline font, bold font, and Plain font, respectively).

FIG. 7C. The disease-specific biomarkers covered as significant variables by the proposed models.

FIG. 8A. Receiver operating characteristic (ROC) plot derived from PLS-DA based on the top 69 ranked variables for control. ROC plot of sensitivity (True Positive Rate, Y-axis) versus 1—specificity (False Positive Rate, X-axis) based on a PLS-DA built upon the 69 markers with the highest contribution for six classes (control, glioblastoma, meningioma, myeloma, pancreas, lung).

FIG. 8B. Receiver operating characteristic (ROC) plot derived from PLS-DA based on the top 69 ranked variables for glioblastoma. ROC plot of sensitivity (True Positive Rate, Y-axis) versus 1—specificity (False Positive Rate, X-axis) based on a PLS-DA built upon the 69 markers with the highest contribution for six classes (control, glioblastoma, meningioma, myeloma, pancreas, lung).

FIG. 8C. Receiver operating characteristic (ROC) plot derived from PLS-DA based on the top 69 ranked variables for meningioma. ROC plot of sensitivity (True Positive Rate, Y-axis) versus 1—specificity (False Positive Rate, X-axis) based on a PLS-DA built upon the 69 markers with the highest contribution for six classes (control, glioblastoma, meningioma, myeloma, pancreas, lung).

FIG. 8D. Receiver operating characteristic (ROC) plot derived from PLS-DA based on the top 69 ranked variables for myeloma. ROC plot of sensitivity (True Positive Rate, Y-axis) versus 1—specificity (False Positive Rate, X-axis) based on a PLS-DA built upon the 69 markers with the highest contribution for six classes (control, glioblastoma, meningioma, myeloma, pancreas, lung).

FIG. 8E. Receiver operating characteristic (ROC) plot derived from PLS-DA based on the top 69 ranked variables for pancreas. ROC plot of sensitivity (True Positive Rate, Y-axis) versus 1—specificity (False Positive Rate, X-axis) based on a PLS-DA built upon the 69 markers with the highest contribution for six classes (control, glioblastoma, meningioma, myeloma, pancreas, lung).

FIG. 8F. Receiver operating characteristic (ROC) plot derived from PLS-DA based on the top 69 ranked variables for lung. ROC plot of sensitivity (True Positive Rate, Y-axis) versus 1—specificity (False Positive Rate, X-axis) based on a PLS-DA built upon the 69 markers with the highest contribution for six classes (control, glioblastoma, meningioma, myeloma, pancreas, lung).

FIG. 9A. Schematic representation of unfolding a three-way data matrix into a two-way matrix.

FIG. 9B. Assignation map obtained by CPANN (14×14) trained using 90 samples (replicates) with all 1823 variables. Sample numbers are indicated on each neuron. The neuron color (assigned label) is decided based on the similarity between the class label (a 6×1 binary vector) and the weight vector in the output layer of the corresponding neuron. Despite using all biomarkers, there are some distinct similarities between samples of the same cancer class. Replicated samples are also mapped on adjacent or the same neurons

FIG. 9C. Classification error of CPANN map was calculated at different map size using 10-fold cross validation.

FIG. 9D. The CPANN network has 69 weight layers, which is equal to the number of variables used to train the model. The i^(th) weight layer reflects the effect of the i^(th) variable (biomarker) on the pattern of the assignation map.

FIG. 9E The correlation of the assignation map and 69 weight layers (weight maps) can be calculated and could help identify the biomarkers related to each cancer class. It can also be visually decided; similarity can be monitored by absolute value of Correlation Coefficient of two maps.

FIG. 9F. The correlation of the assignation map and 69 weight layers (weight maps) can be calculated and could help identify the biomarkers related to each cancer class. It can also be visually decided; similarity can be monitored by absolute value of Correlation Coefficient of two maps.

FIG. 10A. Protein importance for classification vs. percentage of proteins adsorbed on protein corona nanosystem. Panels (a)-(c) illustrate the importance of the observed protein-liposome interactions (‘variables’) in predicting specific cancers. Proteins are grouped by their physiological functions. Panels (d)-(f) illustrate the percentage of proteins adsorbed on each liposome. The protein-liposome groups that emerge as relevant to the prediction of a cancer are highly distinct across cancers (panels (a)-(c)). Moreover, this distinction is substantially more pronounced than the variance in the percentage of proteins adsorbed on the liposomes across those cancers (panels (d)-(f)).

FIG. 10B. Venn diagram showing the number of unique proteins identified in the corona composition of each liposome and their combinations (the table at right presents the same data numerically).

FIG. 10C. Variable importance for classification. Each row indicates the importance of a specific protein. The three dots on each row correspond to the importance of the observed interaction with each of the three liposomes. Horizontal lines straddling the dots indicate the 25th and 75th percentiles of the importance across classifiers trained on 1000 random draws of the training set from the data. These confidence intervals indicate the ‘stability’ of the trained model in terms of the protein-liposome interactions upon which it crucially relies, with respect to random draws of data.

FIG. 11 . Weighted averages of protein-liposome interactions classify cancers. Distribution of the absolute z-scores for each patient group, histogrammed across the 100 most abundant proteins (gray) and previously identified biomarkers (white with black dots). The long black bar corresponds to the z-score for a linear combination of the protein-liposome interactions. A large z-score for a specific protein-liposome interaction indicates that the group ‘separates’ from the rest of the patients in that particular interaction. The figure consequently indicates that whereas no individual protein-liposome interaction suffices to classify any of the cancers, their weighted combinations induce a separation of between 2 and 2.5 standard deviations.

FIG. 12 . Multi-liposomes concentrate low-abundance and rare proteins. Protein corona contribution vs. known plasma concentration, plotted on log-log scale. Each point represents a single protein and liposome, with corona contribution for each disease and healthy individuals, and both corona contribution and plasma concentration are normalized with respect to albumin. Plasma concentrations vary over 10 orders of magnitude, while the liposome array detects these same proteins over 4-5 orders of magnitude. Corona contributions of proteins whose plasma concentration is unknown/unreported are plotted in the red area to the right.

FIG. 13 . Examples of the types of nanoscale sensor elements that can be used for some embodiments of the sensor arrays. Different types of nanoparticles (e.g., organic, inorganic, and polymeric nanoparticles) with various physicochemical properties (e.g., different, surface properties, sizes, and shapes) can be used as sensor elements. Sensor array can be created by minimum two elements to an unlimited number of elements.

FIG. 14 . Example of one method of collection of corona coated particles in in vitro, ex vivo, and in vivo conditions. The particles get incubated with biological fluids (e.g., plasma of patients with different type of disease) and the corona coated particles get collected and stored for analysis.

FIG. 15A. Examples of conjugation of nano-object materials (with different physicochemical properties) to substrates (with different physicochemical properties) to make a protein corona sensor array chip (A) before interactions with protein source (e.g., human plasma of various disease). The specific protein corona will form on the surface of nano-objects, with different physicochemical properties. The substrates may also get coated by several types of proteins, which have negligible effects on the detection efficacy of the chip.

FIG. 15B. Examples of conjugation of nano-object materials (with different physicochemical properties) to substrates (with different physicochemical properties) to make a protein corona sensor array chip after interactions with protein source (e.g., human plasma of various disease).

FIG. 16A. Examples of protein corona sensor array chip with nano-curvatures (produced by wide variety of available approaches like lithography and mold casting), with different physicochemical properties, before interactions with protein source (e.g., human plasma of various disease). The specific protein corona will form on the surface of nano-objects, with different physicochemical properties. The substrates may also get coated by several types of proteins, which have negligible effects on the detection efficacy of the chip.

FIG. 16B. Examples of protein corona sensor array chip with nano-curvatures (produced by wide variety of available approaches like lithography and mold casting), with different physicochemical properties after interactions with protein source (e.g., human plasma of various disease). The specific protein corona will form on the surface of nano-objects, with different physicochemical properties. The substrates may also get coated by several types of proteins, which have negligible effects on the detection efficacy of the chip.

FIG. 17A. Examples of conjugation of nano-object materials (with different physicochemical properties) to substrates (with different physicochemical properties) to make a protein corona sensor array micro/nano fluidic chip before and (b) after interactions with protein source (e.g., human plasma of various disease). The specific protein corona will form on the surface of nano-objects, with different physicochemical properties. The substrates may also get coated by several types of proteins, which have negligible effects on the detection efficacy of the chip.

FIG. 17B. Examples of conjugation of nano-object materials to substrates to make a protein corona sensor array micro/nano fluidic chip after interactions with protein source (e.g., human plasma of various disease). The specific protein corona will form on the surface of nano-objects, with different physicochemical properties.

FIG. 18A. Examples of protein corona sensor array micro/nano fluidic chip with nano-curvatures (produced by wide variety of available approaches like lithography and mold casting), with different physicochemical properties, before interactions with protein source (e.g., human plasma of various disease).

FIG. 18B. Examples of protein corona sensor array micro/nano fluidic chip with nano-curvatures (produced by wide variety of available approaches like lithography and mold casting), with different physicochemical properties, after interactions with protein source (e.g., human plasma of various disease).

FIG. 19A. Examples of conjugation of random-ordered nano-object materials (with different physicochemical properties) to substrates (with different physicochemical properties) to make a protein corona sensor array chip before interactions with protein source (e.g., human plasma of various disease).

FIG. 19B. Examples of conjugation of random-ordered nano-object materials (with different physicochemical properties) to substrates (with different physicochemical properties) to make a protein corona sensor array chip after interactions with protein source (e.g., human plasma of various disease).

FIG. 20A. Examples of protein corona sensor array chip with random-ordered nano-curvatures (produced by wide variety of available approaches like lithography and mold casting), with different physicochemical properties, before interactions with protein source (e.g., human plasma of various disease).

FIG. 20B. Examples of protein corona sensor array chip with random-ordered nano-curvatures with different physicochemical properties after interactions with protein source (e.g., human plasma of various disease).

FIG. 21A. Examples of conjugation of random-ordered nano-object materials (with different physicochemical properties) to substrates (with different physicochemical properties) to make a protein corona sensor array micro/nano fluidic chip (A) before interactions with protein source (e.g., human plasma of various disease).

FIG. 21B. Examples of conjugation of random-ordered nano-object materials to substrates to make a protein corona sensor array micro/nano fluidic chip after interactions with protein source (e.g., human plasma of various disease).

FIG. 22A. Examples of protein corona sensor array micro/nano fluidic chip with random-ordered nano-curvatures (produced by wide variety of available approaches like lithography and mold casting), with different physicochemical properties, before interactions with protein source (e.g., human plasma of various disease).

FIG. 22B. Examples of protein corona sensor array micro/nano fluidic chip with random-ordered nano-curvatures with different physicochemical properties after interactions with protein source (e.g., human plasma of various disease).

FIG. 23 . Example of conjugation of nanoparticles to the silica substrate surface (as representative substrate) via the amidation reaction between the amino groups on silica substrate surface and carboxylic acid groups on nanoparticle surface.

FIG. 24 . Example of conjugation of nanoparticles to the silica substrate surface (as representative substrate) via the ring-opening reaction between the epoxy groups on silica substrate surface and amino groups on nanoparticle surface.

FIG. 25 . Example of conjugation of nanoparticles to the silica substrate surface (as representative substrate) via the Michael Addition reaction between the maleimide groups on silica substrate surface and thiol or amino groups on nanoparticle surface.

FIG. 26 . Example of conjugation of nanoparticles to the silica substrate surface (as representative substrate) via the urethane reaction between the isocyanate groups on silica substrate surface and hydroxyl or amino groups on nanoparticle surface.

FIG. 27 . Example of conjugation of nanoparticles to the silica substrate surface (as representative substrate) via the oxidation reaction between the thiol groups on silica substrate surface and the ones on nanoparticle surface.

FIG. 28 . Example of conjugation of nanoparticles to the silica substrate surface (as representative substrate) via the “Click” chemistry between azide groups on silica substrate surface and alkyne groups on nanoparticle surface.

FIG. 29 . Example of conjugation of nanoparticles to the silica substrate surface (as representative substrate) via the thiol exchange reaction between 2-pyridyldithiol groups on silica substrate surface and thiol groups on nanoparticle surface.

FIG. 30 . Example of conjugation of nanoparticles to the silica substrate surface (as representative substrate) via the coordination reaction between boronic acid groups on silica substrate surface and diol groups on nanoparticle surface.

FIG. 31 . Example of conjugation of nanoparticles to the silica substrate surface (as representative substrate) via the UV light-irradiated addition reaction between C═C bonds on silica substrate surface and C═C bonds on nanoparticle surface.

FIG. 32 . Example of conjugation of nanoparticles to the gold substrate surface (as representative substrate) via Au-thiol bonds.

FIG. 33 Example of conjugation of nanoparticles to the gold substrate surface (as representative substrate) via the amidation reaction between the carboxylic acid groups on gold substrate surface and the amino groups on nanoparticle surface.

FIG. 34 . Example of conjugation of nanoparticles to the gold substrate surface (as representative substrate) via “Click” chemistry between the azide groups on gold substrate surface and the alkyne groups on nanoparticle surface.

FIG. 35 . Example of conjugation of nanoparticles to the gold substrate surface (as representative substrate) via urethane reaction between the NHS groups on gold substrate surface and the amino groups on nanoparticle surface.

FIG. 36 . Example of conjugation of nanoparticles to the silica substrate surface (as representative substrate) via the ring-opening reaction between the epoxy groups on gold substrate surface and amino groups on nanoparticle surface.

FIG. 37 . Example of conjugation of nanoparticles to the gold substrate surface (as representative substrate) via the coordination reaction between boronic acid groups on silica substrate surface and diol groups on nanoparticle surface.

FIG. 38 . Example of conjugation of nanoparticles to the gold substrate surface (as representative substrate) via the UV light-irradiated addition reaction between C═C bonds on gold substrate surface and C═C bonds on nanoparticle surface.

FIG. 39 . Example of conjugation of nanoparticles to the gold substrate surface (as representative substrate) via the “Ligand-Receptor” interaction between biotin on gold substrate surface and avidin on nanoparticle surface.

FIG. 40 . Example of conjugation of nanoparticles to the gold substrate surface (as representative substrate) via the “Host-Guest” interaction between a-cyclodextrin (a-CD) on gold substrate surface and adamantine (Ad) on nanoparticle surface.

FIG. 41 . Dissociation of proteins from the surface of nanoparticles and their corona composition analysis. Analysis of the protein corona sensor array data with supervised and unsupervised approaches to identify and discriminate diseases.

FIG. 42A. Example of sensor array with random order nanoscale sensor elements for fluorescence or luminescence readout.

FIG. 42B. Example of sensor array with random order nanoscale sensor elements for fluorescence or luminescence readout.

FIG. 42C. Example of sensor array with random order nanoscale sensor elements for fluorescence or luminescence readout.

FIG. 42D. Example of sensor array with random order nanoscale sensor elements for fluorescence or luminescence readout.

FIG. 43A. Example of sensor array with order nanoscale sensor elements for fluorescence or luminescence readout.

FIG. 43B. Example of sensor array with order nanoscale sensor elements for fluorescence or luminescence readout.

FIG. 43C. Example of sensor array with order nanoscale sensor elements for fluorescence or luminescence readout.

FIG. 43D. Example of sensor array with order nanoscale sensor elements for fluorescence or luminescence readout.

FIG. 44A. Characterization of bare polystyrene and silica nanoparticles with different functionalization (none, amine modification (NH₂) and carboxyl modification (COOH)), showing the three different polystyrene nanoparticles (non-functionalized, P—NH₂ and P—COOH) used, their sizes, DLS and zeta potential of the bare particles.

FIG. 44B. Characterization of bare polystyrene and silica nanoparticles with different functionalization (none, amine modification (NH₂) and carboxyl modification (COOH)), showing the three different silica nanoparticles (non-functionalized, S—NH₂ and S—COOH) used, their sizes, DLS and zeta potential.

FIG. 44C. Characterization of bare polystyrene and silica nanoparticles with different functionalization (none, amine modification (NH₂) and carboxyl modification (COOH)), showing TEM of bare polystyrene nanoparticle.

FIG. 44D. Characterization of bare polystyrene and silica nanoparticles with different functionalization (none, amine modification (NH₂) and carboxyl modification (COOH)), showing TEM of bare silica nanoparticles.

FIG. 45A. Characterization of protein corona-coated polystyrene and silica nanoparticles with different functionalization (none, amine modification (NH₂) and carboxyl modification (COOH)), showing the sizes, DLS and zeta potential of the protein-corona loaded polystyrene nanoparticles.

FIG. 45B. Characterization of protein corona-coated polystyrene and silica nanoparticles with different functionalization (none, amine modification (NH₂) and carboxyl modification (COOH)), showing the sizes, DLS and zeta potential of the protein-corona loaded silica nanoparticles.

FIG. 45C. Characterization of protein corona-coated polystyrene and silica nanoparticles with different functionalization (none, amine modification (NH₂) and carboxyl modification (COOH)), showing TEM of protein-corona loaded polystyrene nanoparticles.

FIG. 45D. Characterization of protein corona-coated polystyrene and silica nanoparticles with different functionalization (none, amine modification (NH₂) and carboxyl modification (COOH)), showing TEM of protein-corona loaded silica nanoparticles.

FIG. 46 . A diagram of the type of cancer plasma samples screened with the polystyrene and silica nanoparticles.

FIG. 47 . Protein corona profiles of polystyrene and silica nanoparticles (100 nm) with plain, amine-modified and carboxyl-modified surfaces after incubation with plasma of patients having different cancers, analyzed by SDS PAGE.

FIG. 48 . Protein corona profiles of polystyrene and silica nanoparticles (100 nm) with plain, amine-modified and carboxyl-modified surfaces after incubation with plasma of healthy individuals as analyzed by SDS-Page

FIG. 49 . Plot depicting the separation of patients with cancer from the healthy individuals using a sensor array of the present invention.

FIG. 50A. Characterization of polystyrene and silica nanoparticles used for CAD screening, showing profile of bare, CAD, NO CAD, and CONTROL treated nanoparticles.

FIG. 50B. Characterization of polystyrene and silica nanoparticles used for CAD screening, showing zeta potential for the different groups of nanoparticles.

FIG. 50C. Characterization of polystyrene and silica nanoparticles used for CAD screening, showing TEM of the different nanoparticle in the CAD screen.

FIG. 51A. Protein concentrations of different protein corona from analysis of the CAD, NO CAD, and no risk for CAD (CONTROL) nanoparticles, showing Bradford assay of protein concentrations of the different protein coronas.

FIG. 51B. Protein concentrations of different protein corona from analysis of the CAD, NO CAD, and no risk for CAD (CONTROL) nanoparticles, showing personalized protein corona profiles have been analyzed and compared through 1D-SDS-PAGE.

FIG. 51C. Protein concentrations of different protein corona from analysis of the CAD, NO CAD, and no risk for CAD (CONTROL) nanoparticles, showing gel analysis by densitometry determined differences in the amount of protein in the CAD, NO CAD and CONTROL PCs.

FIG. 52 . Bars depicting the differences in the percentage contribution of the top 20 abundant proteins in the PCs.

FIG. 53 . Plot depicting the classification of the subject into CAD, NO CAD and CONTROL by analysis of the fingerprints produced by the protein-coated corona nanoparticles.

FIG. 54A. Synthetic and biological identity of nanoparticles after incubation in Alzheimer's disease plasma. Nanosight nanoparticles tracking analysis (size). Polystyrene nanoparticles before and after coating with AD protein coronas. Bare nanoparticles are 90-100 nm and homogenous in size. AD PC-coated nanoparticles are bigger and less homogenous in size. Intensity profiles and scatter plot of each measurements are reported. Values are average ±SD (n=3).

FIG. 54B. Synthetic and biological identity of nanoparticles after incubation in Alzheimer's disease plasma. Nanosight nanoparticles tracking analysis (size). Silica nanoparticles before and after coating with AD protein coronas. Bare nanoparticles are nm and homogenous in size. AD PC-coated nanoparticles are bigger and less homogenous in size. Intensity profiles and scatter plot of each measurements are reported. Values are average ±SD (n=3).

FIG. 55 . TEM analysis. Nanoparticles before and after coating with AD protein coronas have been analyzed by transmission electron microscopy to evaluate potential changes in morphology and size. P: polystyrene; PN: polystyrene-NH₂, PC: polystyrene-COOH; S: silica; SN: silica-NH₂; SC: silica-COOH. All the nanoparticles show a size increase following incubation in plasma.

FIG. 56 . SDS-PAGE gels and densitometric analysis of the bands. Loading order: P, P—NH₂, P—COOH, S, S—NH₂, S—COOH where P: polystyrene; PN: polystyrene-NH₂, PC: polystyrene-COOH; S: silica; SN: silica-NH₂; SC: silica-COOH. Personalized protein corona profiles have been analyzed and compared through SDS-PAGE. Four representative gels of Alzheimer's protein corona and one healthy protein corona are showed. Intensity of bands relative to plasma proteins adsorbed on nanoparticles was analyzed by Image) (y-axis: intensity, x-axis: molecular weight).

FIG. 57 . Classification of healthy and AD disease. The white dots are AD and black dots are healthy samples.

FIG. 58 . SDS-Page gel analysis of silica nanoparticle of different diameters using the same volume loaded (10 ul, left) or same amount (10 ug, right).

FIG. 59 . Scheme showing the conducted experiments to probe the existence of nucleic acids in biomolecular corona.

FIG. 60 . Agarose gel analysis of nucleic acid binding to three different nanoparticles.

FIG. 61 . Analysis of nucleic acid content in plasma.

FIG. 62 . Analysis of nucleic acid amounts associated with biomolecule corona of a nanoparticle when protein was dissociated from the corona by urea.

FIG. 63 . Analysis of nucleic acid amounts associated with biomolecule corona of a nanoparticle when corona proteins were not dissociated from the surface of the particles.

FIG. 64 . Analysis of nucleic acid amounts associated with biomolecule corona of a nanoparticle when nucleic acids first purified from plasma with purification kit and then incubated with nanoparticles.

FIG. 65 . Schematic diagram of a method of distinguishing states of a complex biological sample.

FIG. 66 . Schematic diagram of a computer system.

FIG. 67 . Table 3. Correlation coefficient of CPANN weight map for each variable in the six classes.

FIG. 68 . Table 9: Information of the patients in which their plasmas were used in Example 6.

DETAILED DESCRIPTION OF THE INVENTION

The present invention has been described in terms of one or more preferred embodiments, and it should be appreciated that many equivalents, alternatives, variations, and modifications, aside from those expressly stated, are possible and within the scope of the invention.

The present invention provides sensor arrays and methods of use for the prognosis, diagnosis and detection of a disease state in a subject. The sensor array of the present invention differs from known sensor arrays that involve individual sensors that detect specific biomolecules. In the present sensor array, the biomolecules do not have to be known, as the system does not rely on the presence or absence of a specific biomolecules or amounts of specific disease markers. This new sensor array is able to detect changes in the compositions of the biomolecule corona associated with the different sensor elements. This ability to detect relative changes or patterns (either the actual biomolecules associated with the different sensor elements or in the amounts and/or conformations of each biomolecule associated with each sensor element) allows for determining a unique biomolecule fingerprint for each array. This biomolecule fingerprint can stratify different health and disease states of subjects. In some embodiments, the biomolecular fingerprint is not only able to differentiate between healthy subjects and subjects in various different stages of a disease or disorder but also to determine a pre-disease state in a subject where the subject will develop the disease or disorder at a later time. This is significantly different and novel over systems in the art that measure or detect specific biomarkers associated with a disease or disorder to provide a predisposition (e.g. a chance or likelihood) of developing the disease. The present sensor and methods is able to detect a disease before any signs or symptoms, in other words, can pre-diagnose the disease before any specific signs or symptoms appear.

The uniqueness of the present invention is the combination of this recognition of a biomolecular fingerprint from a sample from a subject and the ability to determine a disease state for that subject on a continuum of health.

The present invention is based on work by the inventors that have shown that the surface of sensor elements, e.g. nanoparticles, is rapidly covered with a layer of different biomolecules, including proteins, to form a “biomolecule corona” when contacted with a biological sample They type, amount, and categories of the biomolecules that make up these biomolecule corona are strongly related to the physicochemical properties of the sensor elements themselves and the complex interactions between the different biomolecules themselves and the sensor elements. These interactions lead to the production of a unique biomolecule corona signature for each sensor element. In other words, depending on which biomolecules interact with the sensor element not only influences the makeup of the biomolecule corona but also can alter which other different biomolecules can also interact with that specific sensor element.

Different sensor elements each with their own biomolecule corona signature can be contacted with a sample to produce a unique biomolecule fingerprint for that sample. This fingerprint can then be used to determine a disease state of a subject. Embodiments of the invention will be discussed in more detail below.

The present invention provides sensor arrays comprising, consisting essentially of or consists of a plurality of sensor elements wherein the plurality of sensor elements differ from each other in at least one physiocochemical property. In some embodiments, each sensor element is able to bind a plurality of biomolecules in a sample to produce a biomolecule corona signature. In some embodiments, each sensor elements has a distinct biomolecule corona signature.

The plurality of sensor elements when contacted with a sample produces a plurality of biomolecule corona signatures which together form a biomolecule fingerprint. The “biomolecule fingerprint” is the combined composition or pattern of biomolecules of at least two biomolecule corona signatures for the plurality of sensor elements.

As used herein, the term “sensor element” refer to elements that are able to bind to a plurality of biomolecules when in contact with a sample and encompasses the term “nanoscale sensor element”. In one embodiment, the sensor element is an element from about 5 nanometer to about 50000 nanometer in at least one direction. Suitable sensor elements include, for example, but not limited to a sensor element from about 5 nm to about 50,000 nm in at least one direction, including, about 5 nm to about 40000 nm, alternatively about 5 nm to about 30000 nm, alternatively about 5 nm to about 20,000 nm, alternatively about 5 nm to about 10,000 nm, alternatively about 5 nm to about 5000 nm, alternatively about 5 nm to about 1000 nm, alternatively about 5 nm to about 500 nm, alternatively about 5 nm to 50 nm, alternatively about 10 nm to 100 nm, alternatively about 20 nm to 200 nm, alternatively about 30 nm to 300 nm, alternatively about 40 nm to 400 nm, alternatively about 50 nm to 500 nm, alternatively about 60 nm to 600 nm, alternatively about 70 nm to 700 nm, alternatively about 80 nm to 800 nm, alternatively about 90 nm to 900 nm, alternatively about 100 nm to 1000 nm, alternatively about 1000 nm to 10000 nm, alternatively about 10000 nm to 50000 nm and any combination or amount inbetween (e.g. 5 nm, 10 nm, 15 nm, 20 nm, 25 nm, 30 nm, 35 nm, 40 nm, 45 nm, 50 nm, 55 nm, 60 nm, 65 nm, 70 nm, 80 nm, 90 nm, 100 nm, 125 nm, 150 nm, 175 nm, 200 nm, 225 nm, 250 nm, 275 nm, 300 nm, 350 nm, 400 nm, 450 nm, 500 nm, 550 nm, 600 nm, 650 nm, 700 nm, 750 nm, 800 nm, 850 nm, 900 nm, 1000 nm, 1200 nm, 1300 nm, 1400 nm, 1500 nm, 1600 nm, 1700 nm, 1800 nm, 1900 nm, 2000 nm, 2500 nm, 3000 nm, 3500 nm, 4000 nm, 4500 nm, 5000 nm, 5500 nm, 6000 nm, 6500 nm, 7000 nm, 7500 nm, 8000 nm, 8500 nm, 9000 nm, 10000 nm, 11000 nm, 12000 nm, 13000 nm, 14000 nm, 15000 nm, 16000 nm, 17000 nm, 18000 nm, 19000 nm, 20000 nm, 25000 nm, 30000 nm, 35000 nm, 40000 nm, 45000 nm, 50000 nm and any number inbetween). A nanoscale sensor element refers to a sensor element that is less than 1 micron in at least one direction. Suitable examples of ranges of nanoscale sensor elements include, but are not limited to, for example, elements from about 5 nm to about 1000 nm in one direction, including, from example, about 5 nm to about 500 nm, alternatively about 5 nm to about 400 nm, alternatively about 5 nm to about 300 nm, alternatively about 5 nm to about 200 nm, alternatively about 5 nm to about 100 nm, alternatively about 5 nm to about 50 nm, alternatively about 10 nm to about 1000 nm, alternatively about 10 nm to about 750 nm, alternatively about 10 nm to about 500 nm, alternatively about 10 nm to about 250 nm, alternatively about 10 nm to about 200 nm, alternatively about 10 nm to about 100 nm, alternatively about 50 nm to about 1000 nm, alternatively about 50 nm to about 500 nm, alternatively about 50 nm to about 250 nm, alternatively about 50 nm to about 200 nm, alternatively about 50 nm to about 100 nm, and any combinations, ranges or amount inbetween (e.g. 5 nm, 10 nm, 15 nm, 20 nm, 25 nm, 30 nm, 35 nm, 40 nm, 45 nm, 50 nm, 55 nm, 60 nm, 65 nm, 70 nm, 80 nm, 90 nm, 100 nm, 125 nm, 150 nm, 175 nm, 200 nm, 225 nm, 250 nm, 275 nm, 300 nm, 350 nm, 400 nm, 450 nm, 500 nm, 550 nm, 600 nm, 650 nm, 700 nm, 750 nm, 800 nm, 850 nm, 900 nm, 1000 nm, etc.). In reference to the sensor arrays described herein, the use of the term sensor element includes the use of a nanoscale sensor element for the sensor and associated methods.

The term “plurality of sensor elements” refers to more than one, for example, at least two sensor elements. In some embodiments, the plurality of sensor elements includes at least two sensor elements to at least 1000 sensor elements, preferably about two sensor elements to about 100 sensor elements. In suitable embodiments, the array comprises at least two to at least 100 sensor elements, alternatively at least two to at least 50 sensor elements, alternatively at least 2 to 30 sensor elements, alternatively at least 2 to 20 sensor elements, alternatively at least 2 to 10 sensor elements, alternatively at least 3 to at least 50 sensor elements, alternatively at least 3 to at least 30 sensor elements, alternatively at least 3 to at least 20 sensor elements, alternatively at least 3 to at least 10 sensor elements, alternatively at least 4 to at least 50 sensor elements, alternatively at least 4 to at least 30 sensor elements, alternatively at least 4 to at least 20 sensor elements, alternatively at least 4 to at least 10 sensor elements, and including any number of sensor elements contemplated in between (e.g., at least 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 21, 22, 23, 24, 25, 26, 27, 28, 29, 30, 31, 32, 33, 34, 35, 36, 37, 38, 39, 40, 41, 42, 43, 44, 45, 46, 47, 48, 49, 50, 60, 70, 80, 90, 100, 110, 120, 130, 140, 150, 160, 170, 180, 190, 200, 225, 250, 300, 350, 400, 450, 500, 550, 600, 650, 700, 750, 800, etc.). In some embodiments, the sensor array comprises at least 6 sensor elements to at least 20 sensor elements, alternatively at least 6 sensor elements to at least 10 sensor elements.

The term “plurality of nanoscale sensor elements” refers to more than one, for example, at least two nanoscale sensor elements. In some embodiments, the plurality of nanoscale sensor elements includes at least two nanoscale sensor elements to at least 1000 nanoscale sensor elements, preferably about two nanoscale sensor elements to about 100 nanoscale sensor elements. In suitable embodiments, the array comprises at least two to at least 100 nanoscale sensor elements, alternatively at least two to at least nanoscale sensor elements, alternatively at least 2 to 30 nanoscale sensor elements, alternatively at least 2 to 20 nanoscale sensor elements, alternatively at least 2 to 10 nanoscale sensor elements, alternatively at least 3 to at least 50 nanoscale sensor elements, alternatively at least 3 to at least 30 nanoscale sensor elements, alternatively at least 3 to at least 20 nanoscale sensor elements, alternatively at least 3 to at least 10 nanoscale sensor elements, alternatively at least 4 to at least 50 nanoscale sensor elements, alternatively at least 4 to at least 30 nanoscale sensor elements, alternatively at least 4 to at least 20 nanoscale sensor elements, alternatively at least 4 to at least 10 nanoscale sensor elements, and including any number of nanoscale sensor elements contemplated in between (e.g., at least 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 21, 22, 23, 24, 25, 26, 27, 28, 29, 30, 31, 32, 33, 34, 35, 36, 37, 38, 39, 40, 41, 42, 43, 44, 45, 46, 47, 48, 49, 50, 60, 70, 80, 90, 100, 110, 120, 130, 140, 150, 160, 170, 180, 190, 200, 225, 250, 300, 350, 400, 450, 500, 550, 600, 650, 700, 750, 800, etc.).

As used herein, the term “biomolecule corona” refers to the plurality of different biomolecules that are able to bind to a sensor element. The term “biomolecule corona” encompasses “protein corona” which is a term used in the art to refer to the proteins, lipids and other plasma components that bind nanoparticles when they come into contact with biological samples or biological system. For use herein, the term “biomolecule corona” also encompasses both the soft and hard protein corona as referred to in the art, see, e.g., Milani et al. “Reversible versus Irreversible Binding of Transferring to Polystyrene Nanoparticles: Soft and Hard Corona” ACS NANO, 2012, 6(3), pp. 2532-2541; Mirshafiee et al. “Impact of protein pre-coating on the protein corona composition and nanoparticle cellular uptake” Biomaterials vol. 75, January 2016 pp. 295-304, Mahmoudi et al. “Emerging understanding of the protein corona at the nano-bio interfaces” Nanotoday 11(6) December 2016, pp. 817-832, and Mahmoudi et al. “Protein-Nanoparticle Interactions: Opportunities and Challenges” Chem. Rev., 2011, 111(9), pp. 5610-5637, the contents of which are incorporated by reference in their entireties. As described in the art, adsorption curve shows the build-up of a strongly bound monolayer up to the point of monolayer saturation (at a geometrically defined protein-to-NP ratio), beyond which a secondary, weakly bound layer is formed. While the first layer is irreversibly bound (hard corona), the secondary layer (soft corona) exhibits dynamic exchange. Proteins that adsorb with high affinity form what is known as the “hard” corona, consisting of tightly bound proteins that do not readily desorb, and proteins that adsorb with low affinity form the “soft” corona, consisting of loosely bound proteins. Soft and hard corona can also be defined based on their exchange times. Hard corona usually shows much larger exchange times in the order of several hours. See, e.g., M. Rahman et al. Protein-Nanoparticle Interactions, Spring Series in Biophysics 15, 2013, incorporated by reference in its entirety.

The term “biomolecule corona signature” refers to the composition, signature or pattern of different biomolecules that are bound to each separate sensor element. The signature not only refers to the different biomolecules but also the differences in the amount, level or quantity of the biomolecule bound to the sensor element, or differences in the conformational state of the biomolecule that is bound to the sensor element. It is contemplated that the biomolecule corona signatures of each sensor elements may contain some of the same biomolecules, may contain distinct biomolecules with regard to the other sensor elements, and/or may differ in level or quantity, type or confirmation of the biomolecule. The biomolecule corona signature may depend on not only the physiocochemical properties of the sensor element, but also the nature of the sample and the duration of exposure. In some cases, the biomolecule corona signature is a protein corona signature. In another case, the biomolecule corona signature is a polysaccharide corona signature. In yet another case, the biomolecule corona signature is a metabolite corona signature. In some cases, the biomolecule corona signature is a lipidomic corona signature.

In some embodiments, the biomolecule corona signature comprises the biomolecules found in a soft corona and a hard corona. In some embodiments, the soft corona is a soft protein corona. In some embodiments, the hard corona is a hard protein corona.

The term “biomolecule” refers to biological components that may be involved in corona formation, including, but not limited to, for example, proteins, polypeptides, polysaccharides, a sugar, a lipid, a lipoprotein, a metabolite, an oligonucleotide, metabolome or combination thereof. It is contemplated that the biomolecule corona signatures of each sensor elements may contain some of the same biomolecules, may contain distinct biomolecules with regard to the other sensor elements, and/or may differ in level or quantity, type or confirmation of the biomolecule that binds to each sensor element. In one embodiment, the biomolecule is selected from the group of proteins, nucleic acids, lipids, and metabolomes.

In some embodiments, the sensor array comprises, consists essentially of or consists of a first sensor element that produces a first biomolecule corona signature and at least one second sensor element that produces at least one second biomolecule corona signature when the sensor array is contacted with a biological sample. A biomolecule fingerprint is the combination of the first biomolecule signature and the at least one second biomolecule signature. It is contemplated that the biomolecule signature can be made from at least two biomolecule corona signatures to as many different biomolecule signatures are assayed, e.g. at least 1000 different biomolecule corona signatures. The biomolecule corona may be assayed separately for each sensor element to determine the biomolecule corona signature for each element and combined to determine the biomolecule fingerprint or the two or more biomolecule corona can be assayed at the same time to develop the biomolecule fingerprint at once.

In some embodiments, the biomolecule fingerprint includes at least two biomolecule corona signatures. In some embodiments, the biomolecule fingerprint includes at two biomolecule corona signatures to at least 1000 biomolecule corona signatures, preferably about two biomolecule corona signatures to about 100 biomolecule corona signatures. In suitable embodiments, the biomolecule fingerprint comprises at least two to at least 100 biomolecule corona signatures, alternatively at least two to at least 50 biomolecule corona signatures, alternatively at least 2 to 30 biomolecule corona signatures, alternatively at least 2 to 20 biomolecule corona signatures, alternatively at least 2 to 10 biomolecule corona signatures, alternatively at least 3 to at least 50 biomolecule corona signatures, alternatively at least 3 to at least 30 biomolecule corona signatures, alternatively at least 3 to at least 20 biomolecule corona signatures, alternatively at least 3 to at least 10 biomolecule corona signatures, alternatively at least 4 to at least 50 biomolecule corona signatures, alternatively at least 4 to at least 30 biomolecule corona signatures, alternatively at least 4 to at least 20 biomolecule corona signatures, alternatively at least 4 to at least 10 biomolecule corona signatures, and including any number of biomolecule corona signatures contemplated in between (e.g., at least 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 21, 22, 23, 24, 25, 26, 27, 28, 29, 30, 31, 32, 33, 34, 35, 36, 37, 38, 39, 40, 41, 42, 43, 44, 45, 46, 47, 48, 49, 50, 60, 70, 80, 90, 100, 110, 120, 130, 140, 150, 160, 170, 180, 190, 200, 225, 250, 300, 350, 400, 450, 500, 550, 600, 650, 700, 750, 800, etc.).

Advances in proteomic analyses using mass spectrometry have offered new insights into the changes that take place across the spectrum of health and disease including early-stage cancer. Yet the sensitivity and specificity of mass spectrometry approaches have not been adequate for robust early detection of cancers in part due to the high noise created by the 10000 of proteins comprising the human proteome, with estimated concentrations spanning 35-50 mg/ml for albumin to 1-10 pg/ml for some cytokines. The existing technologies have required a trade-off between the depth of coverage and the throughput of processing of plasma proteins. Several attempts have been made to substantially increase the current low levels of protein detection, including depletions of highly abundant proteins, isobaric labeling at the peptide level for multiplexed relative quantification, post-depletion plasma fractionation strategies, biomarker harvesting techniques, mathematical approaches for analyzing high-quality data sets, and multiplexed workflow (i.e., a combination of approaches). Despite such efforts, mass-spectrometry approaches to plasma proteomics have not met with robust success in the early detection of cancers. In fact no prior study, proteomic or otherwise, has reported accurate prediction and classification of a range of cancers, including the earliest pre-symptomatic stages. The present sensor array has provided the first detection system that accurately predicts and classifies a disease state, including pre-symptomatic disease state for a number of different diseases.

Prior attempts have tried to use the “disease-specific protein corona” to identify one cancer type using gel electrophoresis and changes in aggregation size of nanoparticles. However, as we show in the Examples below, the subtle differences in the protein corona at the surface of one type of nanoparticle were not sufficient for robust and accurate identification and discrimination of cancers with acceptable prediction accuracy, mainly due to the persistent issue of inadequate proteomic coverage. The sensory array described herein is able to accurately classify disease states. Not only it is able to predict the disease state, but it is also able to classify patients who are pre-symptomatic of the disease (e.g. Alzheimer's) or classify patients according to the type of disease (e.g. type of cancer).

To materially enhance the capacity of the protein corona for robust and accurate cancer detection with excellent prediction capacity, the inventors developed a sensor array (sometimes referred to herein as a Protein Corona Nanosystem or sensor array nanosystem). Compared with previous approaches limited to the surface of a single nanoparticle, it provides significantly more comprehensive proteomics data over a wider dynamic range of plasma protein concentrations. The sensor array allows for the sampling a complex biological sample (e.g., human plasma sample) using multi-nanoparticles with different physicochemical properties to significantly increase the number and range of both low- and high-abundance proteins identified without protein depletion. This effectively reduces the noise in the vast proteomic information available, yielding more-accurate early differentiation of the proteomic signature that is characteristic of a disease. In addition, because of the combination of protein-nanoparticle and protein-protein interaction that is uniquely derived using the sensor array, each type of protein may be present in different concentrations on the surface of different nanoparticles, providing additional proteomic information. The use of multi-nanoparticles with different physicochemical properties is mainly driven by our recent findings that even small alterations to the physicochemical properties of nanoparticles can elicit dramatic but reproducible changes in the protein corona composition.

The present sensor array has a sensitivity and dynamic range of ten (10) orders of magnitude in terms of protein detection using mass-spectroscopy approaches. The present assay is able to detect proteins that are found in the sub-ng range within a sample. This assay or approach has a much greater dynamic range than current assays for measuring proteins within a sample. For example, mass spectrometry only has a dynamic range 4-6 order of magnitude. This novel sensor array has the ability to sample a greater dynamic range than has previously been achievable. The present sensor array allows for detection and determination of low abundant and rare proteins that we not previously able to be detected.

The term “sample” refers to a biological sample or a complex biological sample obtained from a subject. Suitable biological samples include, but are not limited to, biological fluids, including, but not limited to, systemic blood, plasma, serum, lung lavage, cell lysates, menstrual blood, urine, processed tissue samples, amniotic fluid, cerebrospinal fluid, tears, saliva, semen and the like. In a preferred embodiment, the sample is a blood or serum sample. Blood plasma contains several thousands of different proteins with twelve orders of magnitude differences in the concentrations of these proteins. The present sensor array is able to detect changes within these blood samples over time or over disease states of the subject.

In some embodiments, the biological fluids or complex biological samples are prepared by methods and kits known in the art. For example, some biological samples (e.g. menstrual blood, blood samples, semen, etc.) may first be centrifuged at low speed to remove cell debris, blood clots and other cellular components that may interfere with the array. In other embodiments, for example, tissue specimens may be processed, e.g. tissue samples may be minced or homogenized, treated with enzymes to break up the tissue and/or centrifuged to remove cellular debris allowing for the assaying and extraction of the biomolecules within the tissue samples. Suitable methods of isolating and/or properly preparing and storing blood samples are known in the art, and may include, but are not limited to, the addition of an anti-coagulant agent.

Suitable sensor elements include, but are not limited to, for example, particles, such as organic particles, non-organic particles or combinations thereof. In some embodiments the particles are, for example, nanoparticles, microparticles, micelles, liposomes, iron oxide, graphene, silica, protein-based particles, polystyrene, silver, and gold particles, quantum dots, palladium, platinum, titanium, and combinations thereof. In some embodiments, nanoparticles are liposomes. One skilled in the art would be able to select and prepare suitable particles. In some preferred embodiments, the sensor elements are nanoscale sensor elements. Suitable nanoscale sensor elements are less than 1 micron in at least one direction. In some aspects, the nanoscale sensor elements are less than about 100 nm in at least one direction.

Overview

The present disclosure provides a method of detecting a disease state using a biomolecule corona nanosystem. In one embodiment, the method comprises detecting a disease-specific protein corona.

Sensor Arrays

FIG. 65 shows an exemplary scheme of the presently disclosed array system. As shown at step 1 of FIG. 65 , a complex biological sample (e.g., blood 704) can be collected from a subject 702 expressing a biological state 703 (e.g., a disease state, for example before any physical symptoms of the disease and/or during early and intermediate stages of a disease). Suitable biological samples 704 include, but are not limited to, biological fluids, including, but not limited to, systemic blood, plasma, serum, lung lavage, cell lysates, menstrual blood, urine, processed tissue samples, amniotic fluid, cerebrospinal fluid, tears, saliva, semen and the like. In a preferred embodiment, the sample is a blood or serum sample. In some embodiments, plasma 706 of can be separated from blood cells 708 of subjects expressing a biological state 703 (e.g. healthy people (non-disease state) and cancer patients (disease state), as shown at step 2 of FIG. 65 .

Next, as shown at step 3 of FIG. 65 , a complex biological sample (e.g., plasma 706) can be incubated with a sensor array 710 comprising a plurality of particles 712 with different physicochemical properties. The plurality of particles 712 can be incubated with the plasma 706 to allow biomolecules in the plasma 706 (e.g., proteins in the plasma 706) to bind to one or more of the particles 712. Subsequently, as shown at step 4 of FIG. 65 , the biomolecules (e.g. proteins) bound to the particles 712 can be isolated in a protein solution 714 for further analysis, for example to determine the compositions of the proteins bound to each type of particle 712 (e.g., anionic, neutral and cationic particles 712).

The protein solution 714 can be characterized by, for example as shown at step 5 of FIG. 65 , liquid chromatography-tandem mass spectrometry (LC-MS/MS) 716. Proteins identified using LC-MS/MS 716 can then be analyzed at step 6 of FIG. 65 to determine a biomolecule fingerprint 718 (e.g. representative of proteins, nucleic acids, lipids and polysaccharides that bind to one or more of particles 712) associated with the biological state 703.

At step 7 of FIG. 65 , a computer 720 (e.g., computer system 101 in FIG. 66 ) can be used to associate a biomolecule fingerprint 718 (e.g., protein fingerprint) with a biological state 703 (e.g. health state, disease state). For example, analysis of a biomolecule fingerprint 718 (e.g. protein fingerprint) of at least two samples (e.g. complex biological samples such as plasma 706) can be conducted with a computer system 720 to generate an association 722 between the biological state 703 and the biomolecule fingerprint 718 (at step 8 of FIG. 65 ). The generation of association 722 can be by an association analysis or statistical classification using methods known in the art, including, but not limited to, a wide variety of supervised and unsupervised data analysis and clustering approaches such as hierarchical cluster analysis (HCA), principal component analysis (PCA), Partial least squares Discriminant Analysis (PLS-DA), machine learning (also known as random forest), logistic regression, decision trees, support vector machine (SVM), k-nearest neighbors, naive bayes, linear regression, polynomial regression, SVM for regression, K-means clustering, and hidden Markov models, among others. In other words, the biomolecule fingerprint 718 of each sample (e.g. plasma 706) are compared/analyzed (e.g. using a computer 720) with each other to determine with statistical significance what patterns are common between the individual fingerprints to determine a biological state that is associated with the biomolecule (e.g. protein) fingerprint 718.

The association 722 can link the biomolecule fingerprint 718 (e.g., protein fingerprint) to a wide variety of biological states 703. For example, comparison of biomolecule fingerprints 718 between a subject 702 diagnosed with a disease (i.e., biological state 703 is a disease state) and a subject 702 not diagnosed with the disease (i.e., biological state 703 is a non-disease state) can give rise to an association 722 between the biomolecule fingerprint 718 of the subject 702 with the disease and the disease state. Such an association 722 between the biomarker fingerprint 718 and the disease state (i.e., biological state 703) can in some embodiments be determined very early during the progression of a disease (i.e., before any physical symptoms of the disease manifest and/or before diagnosis of the disease) or at later times during disease progression.

Other examples of biological states 703 that can be associated with a biomolecule fingerprint 718 include responsiveness or non-responsiveness to a drug or pharmaceutical, level of activation of the immune system (e.g., due to exposure of a subject to an exogenous antigen), susceptibility of a subject to adverse effects associated with administration of a drug, and identification of a subject's potential to exhibit an allergic reaction to administration of a particular composition or substance.

Computer Control Systems

The present disclosure provides computer control systems that are programmed to implement methods of the disclosure. FIG. 66 shows a computer system 100 that is programmed or otherwise configured to associate a biomolecule fingerprint 718 with a biological state 703. This determination, analysis or statistical classification is done by methods known in the art, including, but not limited to, for example, a wide variety of supervised and unsupervised data analysis and clustering approaches such as hierarchical cluster analysis (HCA), principal component analysis (PCA), Partial least squares Discriminant Analysis (PLS-DA), machine learning (also known as random forest), logistic regression, decision trees, support vector machine (SVM), k-nearest neighbors, naive bayes, linear regression, polynomial regression, SVM for regression, K-means clustering, and hidden Markov models, among others. The computer system 100 can perform various aspects of analyzing the biomolecule fingerprints 718 of the present disclosure, such as, for example, comparing/analyzing the biomolecule corona of several samples to determine with statistical significance what patterns are common between the individual biomolecule coronas to determine a biomolecule fingerprint 718 that is associated with the biological state 703. The computer system can be used to develop classifiers to detect and discriminate different biomolecule fingerprints 718 (e.g., characteristic of the composition of a protein corona). Data collected from the presently disclosed sensor array can be used to train a machine learning algorithm, specifically an algorithm that receives array measurements from a patient and outputs specific biomolecule corona compositions from each patient. Before training the algorithm, raw data from the array can be first denoised to reduce variability in individual variables.

Machine learning can be generalized as the ability of a learning machine to perform accurately on new, unseen examples/tasks after having experienced a learning data set. Machine learning may include the following concepts and methods. Supervised learning concepts may include AODE; Artificial neural network, such as Backpropagation, Autoencoders, Hopfield networks, Boltzmann machines, Restricted Boltzmann Machines, and Spiking neural networks; Bayesian statistics, such as Bayesian network and Bayesian knowledge base; Case-based reasoning; Gaussian process regression; Gene expression programming; Group method of data handling (GMDH); Inductive logic programming; Instance-based learning; Lazy learning; Learning Automata; Learning Vector Quantization; Logistic Model Tree; Minimum message length (decision trees, decision graphs, etc.), such as Nearest Neighbor Algorithm and Analogical modeling; Probably approximately correct learning (PAC) learning; Ripple down rules, a knowledge acquisition methodology; Symbolic machine learning algorithms; Support vector machines; Random Forests; Ensembles of classifiers, such as Bootstrap aggregating (bagging) and Boosting (meta-algorithm); Ordinal classification; Information fuzzy networks (IFN); Conditional Random Field; ANOVA; Linear classifiers, such as Fisher's linear discriminant, Linear regression, Logistic regression, Multinomial logistic regression, Naive Bayes classifier, Perceptron, Support vector machines; Quadratic classifiers; k-nearest neighbor; Boosting; Decision trees, such as C4.5, Random forests, ID3, CART, SLIQ SPRINT; Bayesian networks, such as Naive Bayes; and Hidden Markov models. Unsupervised learning concepts may include; Expectation-maximization algorithm; Vector Quantization; Generative topographic map; Information bottleneck method; Artificial neural network, such as Self-organizing map; Association rule learning, such as, Apriori algorithm, Eclat algorithm, and FP-growth algorithm; Hierarchical clustering, such as Single-linkage clustering and Conceptual clustering; Cluster analysis, such as, K-means algorithm, Fuzzy clustering, DBSCAN, and OPTICS algorithm; and Outlier Detection, such as Local Outlier Factor. Semi-supervised learning concepts may include; Generative models; Low-density separation; Graph-based methods; and Co-training. Reinforcement learning concepts may include; Temporal difference learning; Q-learning; Learning Automata; and SARSA. Deep learning concepts may include; Deep belief networks; Deep Boltzmann machines; Deep Convolutional neural networks; Deep Recurrent neural networks; and Hierarchical temporal memory.

The computer system 100 depicted in FIG. 66 is adapted to implement a method described herein. The system 100 includes a central computer server 101 that is programmed to implement exemplary methods described herein. The server 101 includes a central processing unit (CPU, also “processor”) 105 which can be a single core processor, a multi core processor, or plurality of processors for parallel processing. The server 101 also includes memory 110 (e.g., random access memory, read-only memory, flash memory); electronic storage unit 115 (e.g. hard disk); communications interface 120 (e.g., network adaptor) for communicating with one or more other systems; and peripheral devices 125 which may include cache, other memory, data storage, and/or electronic display adaptors. The memory 110, storage unit 115, interface 120, and peripheral devices 125 are in communication with the processor 105 through a communications bus (solid lines), such as a motherboard. The storage unit 115 can be a data storage unit for storing data. The server 101 is operatively coupled to a computer network (“network”) 130 with the aid of the communications interface 120. The network 130 can be the Internet, an intranet and/or an extranet, an intranet and/or extranet that is in communication with the Internet, a telecommunication or data network. The network 130 in some cases, with the aid of the server 101, can implement a peer-to-peer network, which may enable devices coupled to the server 101 to behave as a client or a server.

The storage unit 115 can store files, such as subject reports, and/or communications with the data about individuals, or any aspect of data associated with the present disclosure.

The computer server 101 can communicate with one or more remote computer systems through the network 130. The one or more remote computer systems may be, for example, personal computers, laptops, tablets, telephones, Smart phones, or personal digital assistants.

In some applications the computer system 100 includes a single server 101. In other situations, the system includes multiple servers in communication with one another through an intranet, extranet and/or the internet.

The server 101 can be adapted to store measurement data or a database as provided herein, patient information from the subject, such as, for example, medical history, family history, demographic data and/or other clinical or personal information of potential relevance to a particular application. Such information can be stored on the storage unit 115 or the server 101 and such data can be transmitted through a network.

Methods as described herein can be implemented by way of machine (or computer processor) executable code (or software) stored on an electronic storage location of the server 101, such as, for example, on the memory 110, or electronic storage unit 115. During use, the code can be executed by the processor 105. In some cases, the code can be retrieved from the storage unit 115 and stored on the memory 110 for ready access by the processor 105. In some situations, the electronic storage unit 115 can be precluded, and machine-executable instructions are stored on memory 110. Alternatively, the code can be executed on a second computer system 140.

Aspects of the systems and methods provided herein, such as the server 101, can be embodied in programming. Various aspects of the technology may be thought of as “products” or “articles of manufacture” typically in the form of machine (or processor) executable code and/or associated data that is carried on or embodied in a type of machine readable medium. Machine-executable code can be stored on an electronic storage unit, such memory (e.g., read-only memory, random-access memory, flash memory) or a hard disk. “Storage” type media can include any or all of the tangible memory of the computers, processors or the like, or associated modules thereof, such as various semiconductor memories, tape drives, disk drives and the like, which may provide non-transitory storage at any time for the software programming. All or portions of the software may at times be communicated through the Internet or various other telecommunication networks. Such communications, for example, may enable loading of the software from one computer or processor into another, for example, from a management server or host computer into the computer platform of an application server. Thus, another type of media that may bear the software elements includes optical, electrical, and electromagnetic waves, such as used across physical interfaces between local devices, through wired and optical landline networks and over various air-links. The physical elements that carry such waves, such as wired or wireless likes, optical links, or the like, also may be considered as media bearing the software. As used herein, unless restricted to non-transitory, tangible “storage” media, terms such as computer or machine “readable medium” can refer to any medium that participates in providing instructions to a processor for execution.

The computer systems described herein may comprise computer-executable code for performing any of the algorithms or algorithms-based methods described herein. In some applications the algorithms described herein will make use of a memory unit that is comprised of at least one database.

Data relating to the present disclosure can be transmitted over a network or connections for reception and/or review by a receiver. The receiver can be but is not limited to the subject to whom the report pertains; or to a caregiver thereof, e.g., a health care provider, manager, other health care professional, or other caretaker; a person or entity that performed and/or ordered the analysis. The receiver can also be a local or remote system for storing such reports (e.g. servers or other systems of a “cloud computing” architecture). In one embodiment, a computer-readable medium includes a medium suitable for transmission of a result of an analysis of a biological sample using the methods described herein.

Aspects of the systems and methods provided herein, such as the computer system 101 in FIG. 66 can be embodied in programming. Various aspects of the technology may be thought of as “products” or “articles of manufacture” typically in the form of machine (or processor) executable code and/or associated data that is carried on or embodied in a type of machine readable medium. Machine-executable code can be stored on an electronic storage unit, such as memory (e.g., read-only memory, random-access memory, flash memory) or a hard disk. “Storage” type media can include any or all of the tangible memory of the computers, processors or the like, or associated modules thereof, such as various semiconductor memories, tape drives, disk drives and the like, which may provide non-transitory storage at any time for the software programming. All or portions of the software may at times be communicated through the Internet or various other telecommunication networks. Such communications, for example, may enable loading of the software from one computer or processor into another, for example, from a management server or host computer into the computer platform of an application server. Thus, another type of media that may bear the software elements includes optical, electrical and electromagnetic waves, such as used across physical interfaces between local devices, through wired and optical landline networks and over various air-links. The physical elements that carry such waves, such as wired or wireless links, optical links or the like, also may be considered as media bearing the software. As used herein, unless restricted to non-transitory, tangible “storage” media, terms such as computer or machine “readable medium” refer to any medium that participates in providing instructions to a processor for execution.

Hence, a machine readable medium, such as computer-executable code, may take many forms, including but not limited to, a tangible storage medium, a carrier wave medium or physical transmission medium. Non-volatile storage media include, for example, optical or magnetic disks, such as any of the storage devices in any computer (s) or the like, such as may be used to implement the databases, etc. shown in the drawings. Volatile storage media include dynamic memory, such as main memory of such a computer platform. Tangible transmission media include coaxial cables; copper wire and fiber optics, including the wires that comprise a bus within a computer system. Carrier-wave transmission media may take the form of electric or electromagnetic signals, or acoustic or light waves such as those generated during radio frequency (RF) and infrared (IR) data communications. Common forms of computer-readable media therefore include for example: a floppy disk, a flexible disk, hard disk, magnetic tape, any other magnetic medium, a CD-ROM, DVD or DVD-ROM, any other optical medium, punch cards paper tape, any other physical storage medium with patterns of holes, a RAM, a ROM, a PROM and EPROM, a FLASH-EPROM, any other memory chip or cartridge, a carrier wave transporting data or instructions, cables or links transporting such a carrier wave, or any other medium from which a computer may read programming code and/or data. Many of these forms of computer readable media may be involved in carrying one or more sequences of one or more instructions to a processor for execution.

Physicochemical Properties

In some embodiments, the plurality of sensor elements comprises, consists essentially of, or consists of a plurality of particles, wherein each particle is differentiated for each other by at least one physiocochemical property such that each sensor element has a unique biomolecule corona signature when placed in contact with the same sample.

The physiocochemical property of the sensor element found in an array refer to, for example, the composition, size, surface charge, hydrophobicity, hydrophilicity, surface functionality (surface functional groups), surface topography, surface curvature and shape. The term composition encompasses the use of different types of materials and differences in the chemical and/or physical properties of materials, for example, conductivity of the material chosen between the sensor elements.

Surface curvature is generally determined by the nanoparticle size. Thus, at a nanometer scale, as the size of the nanoparticles changes, the surface curvature of the particle changes, and this change of the surface curvature affects the binding selectivity of the surface. For example, at certain curvature, the surface of the particle may have a binding affinity for a specific type of biomolecule where a different curvature will have a different binding affinity and/or a binding affinity for a different biomolecule. The curvature can be adjusted to create a plurality of sensor elements with altered affinity for different biomolecules. A sensor array can be created including a plurality of sensor elements having different curvatures (e.g. different sizes) which results in a plurality of sensor elements each with a different biomolecule corona signature.

Surface morphology may also be modified by methods such as patterning the surface to provide different affinities, engineering surface curvatures on multiple length scales and the like. Patterning the surface is provided by, for example, forming the sensor elements by block polymerization in which the at least two blocks have different chemistries, forming the nanoparticles using mixtures of at least two different polymers and phase separating the polymers during polymerization, and/or cross-linking the separate polymers following phase separation. Engineered surface curvature on multiple length scales is provided, for example, by employing Pickering emulsions (Sacanna et al. 2007) stabilized by finely divided particles for the synthesis of nanoparticles. In some embodiments, finely dividend particles are selected from, for example, silicates, aluminates, titanates, metal oxides such as aluminum, silicon, titanium, nickel, cobalt, iron, manganese, chromium, or vanadium oxides, carbo blacks, and nitrides or carbides, e.g., boron nitride, boron carbide, silicon nitride, or silicon carbide, among others.

For example, the sensor elements including nanoscale sensor elements may each be functionalized to have different physicochemical properties. Suitable methods of functionalizing the sensor elements are known in the art and depend on composition of the sensor element (e.g. gold, iron oxide, silica, silver, etc.), and include, but not limited to, for example aminopropyl functionalized, amine functionalized, boronic acid functionalized, carboxylic acid functionalized, methyl functionalized, N-succinimidyl ester functionalized, PEG functionalized, streptavidin functionalized, methyl ether functionalized, triethoxylpropylaminosilane functionalized, thiol functionalized, PCP functionalized, citrate functionalized, lipoic acid functionalized, BPEI functionalized, carboxyl functionalized, hydroxyl functionalized, and the like. In one embodiment, the nanoparticles may be functionalized with an amine group (—NH₂ or a carboxyl group (COOH). In some embodiments, the nanoscale sensor elements are functionalized with a polar functional group. Non-limiting examples of the polar functional group comprise carboxyl group, a hydroxyl group, a thiol group, a cyano group, a nitro group, an ammonium group, an imidazolium group, a sulfonium group, a pyridinium group, a pyrrolidinium group, a phosphonium group or any combination thereof. In some embodiments, the functional group is an acidic functional group (e.g., sulfonic acid group, carboxyl group, and the like), a basic functional group (e.g., amino group, cyclic secondary amino group (such as pyrrolidyl group and piperidyl group), pyridyl group, imidazole group, guanidine group, etc.), a carbamoyl group, a hydroxyl group, an aldehyde group and the like. In some embodiments, the polar functional group is an ionic functional group. Non-limiting examples of the ionic function group comprise an ammonium group, an imidazolium group, a sulfonium group, a pyridinium group, a pyrrolidinium group, a phosphonium group. In some embodiments, the sensor elements are functionalized with a polymerizable functional group. Non-limiting examples of the polymerizable functional group include a vinyl group and a (meth)acrylic group. In some embodiments, the functional group is pyrrolidyl acrylate, acrylic acid, methacrylic acid, acrylamide, 2-(dimethylamino)ethyl methacrylate, hydroxyethyl methacrylate and the like.

In other embodiments, the physiocochemical properties of the sensor elements may be modified by modification of the surface charge. For example, the surface can be modified to provide a net neutral charge, a net positive surface charge, a net negative surface charge, or a zwitterionic charge. The charge of the surface can be controlled either during synthesis of the element or by post-synthesis modification of the charge through surface functionalization. For polymeric nanoparticles, differences in charge can be obtained during synthesis by using different synthesis procedures, different charged comonomers, and in inorganic substances by having mixed oxidation states.

Nanoparticles

In some embodiments, the particles are nanoparticles. In some embodiments, the particles are liposomes. The liposomes may comprise any lipid capable of forming a particle. The term “lipid” refers to a group of organic compounds that are esters of fatty acids and are characterized by being insoluble in water but soluble in many organic solvents. Lipids are usually divided in at least three classes: (1) “simple lipids” which include fats and oils as well as waxes; (2) “compound lipids” which include phospholipids and glycolipids; and (3) “derived lipids” such as steroids. In one embodiment, the liposome comprises one or more cationic lipids or anionic lipids, and one or more stabilizing lipids. Suitable liposomes are known in the art and include, but are not limited to, for example, DOPG (1,2-dioleoyl-sn-glycero-3-phospho-(1′-rac-glycerol), DOTAP (1,2-Dioleiyl-3 trimethylammonium-propane)-DOPE (dioleoylphosphatidylethanolamine), CHOL (DOPC-Cholesterol), and combinations thereof.

The lipid-based surface of a liposome can contact a subset of biomolecules (e.g., proteins) of a complex biological sample (e.g., plasma, or any sample having a complex mix of biomolecules such as proteins and nucleic acid and at least one of a polysaccharide and lipid) at a lipid-biomolecule (e.g. protein) interface, thereby binding the subset of proteins to produce a pattern of biomolecule (e.g. protein) binding.

In one embodiment, the liposome comprises a cationic lipid. As used herein, the term “cationic lipid” refers to a lipid that is cationic or becomes cationic (protonated) as the pH is lowered below the pK of the ionizable group of the lipid, but is progressively more neutral at higher pH values. At pH values below the pK, the lipid is then able to associate with negatively charged nucleic acids. In certain embodiments, the cationic lipid comprises a zwitterionic lipid that assumes a positive charge on pH decrease. In certain embodiments, the liposomes comprise cationic lipid. In some embodiments, cationic lipid comprises any of a number of lipid species which carry a net positive charge at a selective pH, such as physiological pH. Such lipids include, but are not limited to, N,N-dioleyl-N,N-dimethylammonium chloride (DODAC); N-(2,3-dioleyloxy)propyl)-N,N,N-trimethylammonium chloride (DOTMA); N,N-distearyl-N,N-dimethylammonium bromide (DDAB); N-(2,3-dioleoyloxy)propyl)-N,N,N-trimethylammonium chloride (DOTAP); 3-(N-(N′,N′-dimethylaminoethane)-carbamoyl)cholesterol (DC-Chol), N-(1-(2,3-dioleoyloxy)propyl)-N-2 isperminecarboxamido)ethyl)-N,N-dimethy-lammonium trifluoracetate (DOSPA), dioctadecylamidoglycyl carboxyspermine (DOGS), 1,2-dioleoyl-3-dimethylammonium propane (DODAP), N,N-dimethyl-2,3-dioleoyloxy) propylamine (DODMA), N-(1,2-dimyristyloxyprop-3-yl)-N,N-dimethyl-N-hydroxyethyl ammonium bromide (DMRIE), 1,2-dioleoyl-sn-3-phosphoethanolamine (DOPE), N-(1-(2,3-dioleyloxy)propyl)-N-(2 isperminecarboxamido)ethyl)-N,N-dimethy-lammonium trifluoroacetate (DOSPA), dioctadecylamidoglycyl carboxyspermine (DOGS), and 1,2-ditetradecanoyl-sn-glycero-3-phosphocholine (DMPC). The following lipids are cationic and have a positive charge at below physiological pH: DODAP, DODMA, DMDMA, 1,2-dilinoleyloxy-N,N-dimethylaminopropane (DLinDMA), 1,2-dilinolenyloxy-N,N-dimethylaminopropane (DLenDMA). In some embodiment, the lipid is an amino lipid.

In certain embodiments, the liposome comprises one or more additional lipids which stabilize the formation of particles during their formation. Suitable stabilizing lipids include neutral lipids and anionic lipids. The term “neutral lipid” refers to any one of a number of lipid species that exist in either an uncharged or neutral zwitterionic form at physiological pH. Representative neutral lipids include diaclphosphatidylcholines, diacylphosphatidylethanolamines, ceramides, sphingomyelins, dihydro sphingomyelins, cephalins, and cerebrosides. Exemplary neutral lipids include, for example, distearoylphosphatidylcholine (DSPC), dioleoylphosphatidylcholine (DOPC), dipalmitoylphosphatidylcholine (DPPC), dioleoylphosphatidylglycerol (DOPG), dipalmitoylphosphatidylglycerol (DPPG), dioleoyl-phosphatidylethanolamine (DOPE), palmitoyloleoylphosphatidylcholine (POPC), palmitoyloleoyl-phosphatidylethanolamine (POPE) and dioleoyl-phosphatidylethanolamine 4-(N-maleimidomethyl)-cyclohexane-1-carboxylate (DOPE-mal), dipalmitoyl phosphatidyl ethanolamine (DPPE), dimyristoylphosphoethanolamine (DMPE), distearoyl-phosphatidylethanolamine (DSPE), 16-O-monomethyl PE, 16-O-dimethyl PE, 18-1-trans PE, 1-stearioyl-2-oleoyl-phosphatidyethanol amine (SOPE), and 1,2-dielaidoyl-sn-glycero-3-phophoethanolamine (transDOPE). In one embodiment, the neutral lipid is 1,2-distearoyl-sn-glycero-3-phosphocholine (DSPC).

The lipid nanoparticles may comprise liposomes that include phospholipids. The liposomes may include phosphatidylcholine. Components of the liposomes may also include variants of polyethylene glycol (PEG). For example, the PEG may be branched. The PEG may be unbranched. The PEG may comprise a chemical structure of the following formula: H—(O—CH₂—CH₂)_(n)—OH, where n is an integer from 2-200.

The term “anionic lipid” refers to any lipid that is negatively charged at physiological pH. These lipids include phosphatidylglycerol, cardiolipin diacylphosphatidylserine, diacylphosphatidic acid, N-dodecanoylphosphatidylethanolamines, N-succinylphosphatidylethanolamines, N-glutarylphosphatidylethanolamines, lysylphosphatidyiglycerols, palmitoyloleyolphosphatidylglycerol (POPG), and other anionic modifying groups joined to neutral lipids. In certain embodiments, the liposome comprises glycolipids (e.g., monosialoganglioside GM.sub.1). In certain embodiments, the liposome comprises a sterol, such as cholesterol. In certain embodiments, the liposome comprises an additional, stabilizing-lipid which is a polyethylene glycol-lipid. Suitable polyethylene glycol-lipids include PEG-modified phosphatidylethanolamine, PEG-modified phosphatidic acid, PEG-modified ceramides (e.g., PEG-CerC14 or PEG-CerC20), PEG-modified dialkylamines, PEG-modified diacylglycerols, PEG-modified dialkylglycerols. Representative polyethylene glycol-lipids include PEG-c-DOMG, PEG-c-DMA, and PEG-s-DMG. In one embodiment, the polyethylene glycol-lipid is N-[(methoxy poly(ethylene glycol).sub.2000)carbamyl]-1,2-dimyristyloxlpropyl-3-amine (PEG-c-DMA). In one embodiment, the polyethylene glycol-lipid is PEG-c-DOMG).

Suitable liposomes may be solid lipid nanoparticles (SLN) which can be made of solid lipid, emulsifier and/or water/solvent. SLN may include, but are not limited to, a combination of the following ingredients: triglycerides (tri-stearin), partial glycerides (Imwitor), fatty acids (stearic acid, palmitic acid), and steroids (cholesterol) and waxes (cetyl palmitate). Various emulsifiers and their combination (Pluronic F 68, F 127) have been used to stabilize the lipid dispersion. Suitable ingredients for the use in preparing SNL sensor elements include, but are not limited to, e.g., phospholipids, glycerol, poloxamer 188, soy phosphatidyl choline, compritol, cetyl palmitate, PEG 2000, PEG 4500, Tween® 85, ethyl oleate, Na alginate, ethanol/butanol, tristearin glyceride, PEG 400, isopropyl myristate, Pluronic F68, Tween® 80, trimyristin, tristearin, trilaurin, stearic acid, glyceryl caprate as Capmul®MCM C10, theobroma oil, triglyceride coconut oil, 1-octadecanol, glycerol behenate as Compritol® 888 ATO, glycerol palmitostearate as Precirol® ATO 5, and cetyl palmitate wax and the like.

In some embodiments, the plurality of sensor elements comprise, consist essentially of, or consist of a plurality of half particles of different geometric shapes which can be made by molding technology, 3D printing or 4D printing. Suitable half particles are known in the art, and include, but are not limited to half and partial particles in any geometric shape, for example, spheres, rods, triangles, cubes and combinations thereof. Suitably, in one embodiment, the plurality of half particles have different physicochemical properties made by 3-D printing.

In some embodiments, the sensor elements, including nanoscale sensor elements, are made by 3D or 4 D printing. Suitable methods of 3D and 4D printing of sensor elements, including nanoscale sensor elements are known in the art. Suitable material for 3D and 4D printing include, but is not limited to, e.g., plastics and synthetic polymers (e.g., poly-ethylene glycol-diacrylate (PEG-DA), poly (e-caprolactone) (PCL), poly(propylene oxide (PPO), poly(ethylene oxide) (PEO) etc.), metals, powders, glass, ceramics, and hydrogels. Suitable shapes made by 3D or 4D printing include, but are not limited to, for example, full or partial spheres (e.g. ¾ or half spheres), rods, cubes, triangles or other geometrical or non-geometrical shapes.

3D printing techniques include, but are not limited to, microextrusion printing, inkjet bioprinting, laser-assisted bioprinting, stereolithography, omnidirectional printing, and stamp printing.

In some embodiments, the nanoscale sensor elements are nanoparticles. Suitable nanoparticles are known in the art and include, but are not limited to, for example, natural or synthetic polymers, copolymers, terpolymers (with the cores being composed of metals or inorganic oxides, including magnetic cores). Suitable polymeric nanoparticles include, but are not limited to, e.g., polystyrene; poly(lysine), chitosan, dextran, poly(acrylamide) and its derivatives usch as N-isopropylacrylamide, N-tertbutylacrylamide, N,N-dimethylacrylamide, polyethylene glycol, poly(vinyl alcohol), gelatin, starch, degradable (bio)polymers, silica and the like.

In various embodiments, the core of the nanoparticles can include an organic particle, an inorganic particle, or a particle including both organic and inorganic materials. For example, the particles can have a core structure that is or includes a metal particle, a quantum dot particle, a metal oxide particle, or a core-shell particle. For example, the core structure can be or include a polymeric particle or a lipid-based particle, and the linkers can include a lipid, a surfactant, a polymer, a hydrocarbon chain, or an amphiphilic polymer. For example, the linkers can include polyethylene glycol or polyalkylene glycol, e.g., the first ends of the linkers can include a lipid bound to polyethelene glycol (PEG) and the second ends can include functional groups bound to the PEG. In these methods, the first or second functional groups can include an amine group, a maleimide group, a hydroxyl group, a carboxyl group, a pyridylthiol group, or an azide group.

In certain embodiments, the nanoparticles can comprise polymers that include, for example, a sodium polystyrene sulfonate (PSS), polyethylene oxide (PEO), polyoxyethylene glycol, polyethylene glycol (PEG), polyethylene imine (PEI), polylactic acid, polycaprolactone, polyglycolic acid, poly(lactide-co-glycolide polymer (PLGA), cellulose ether polymer, polyvinylpyrrolidone, vinyl acetate, polyvinylpyrrolidone-vinyl acetate copolymer, polyvinyl alcohol (PVA), acrylate, polyacrylic acid (PAA), vinyl acetate, crotonic acid copolymers, polyacrylamide, polyethylene phosphonate, polybutene phosphonate, polystyrene, polyvinylphosphonate, polyalkylene, carboxy vinyl polymer, sodium alginate, carrageenan, xanthan gum, gum acacia, Arabic gum, guar gum, pullulan, agar, chitin, chitosan, pectin, karaya gum, locust bean gum, maltodextrin, amylose, corn starch, potato starch, rice starch, tapioca starch, pea starch, sweet potato starch, barley starch, wheat starch, hydroxypropylated high amylose starch, dextrin, levan, elsinan, gluten, collagen, whey protein isolate, casein, milk protein, soy protein, keratin, or a gelatin, or a copolymer, derivative, or mixture thereof.

In other embodiments, the polymer can be or include a polyethylene, polycarbonate, polyanhydride, polyhydroxyacid, polypropylfumerate, polycaprolactone, polyamide, polyacetal, polyether, polyester, poly(orthoester), polycyanoacrylate, polyvinyl alcohol, polyurethane, polyphosphazene, polyacrylate, polymethacrylate, polycyanoacrylate, polyurea, polystyrene, or a polyamine, or a copolymer, derivative, or mixture thereof.

In some embodiments, the present disclosure provides nanoparticles comprising biodegradable polymers. The non-limiting exemplary biodegradable polymers can be poly-β-amino-esters (PBAEs), poly(amido amines), polyesters including poly lactic-co-glycolic acid (PLGA), polyanhydrides, bioreducible polymers, and other biodegradable polymers. In some embodiments, the biodegradable polymer comprises 2-(3-aminopropylamino)ethanol end-modified poly(1,4-butanediol diacrylate-co-4-amino-1-butanol), (1-(3-aminopropyl)-4-methylpiperazine end-modified poly(1,4-butanediol diacrylate-co-4-amino-1-butanol), 2-(3-aminopropylamino)ethanol end-modified poly(1,4-butanediol diacrylate-co-5-amino-1-pentanol), (1-(3-aminopropyl)-4-methylpiperazine end-modified poly(1,4-butanediol diacrylate-co-5-amino-1-pentanol), 2-(3-aminopropylamino)ethanol end-modified poly(1,5 pentanediol diacrylate-co-3-amino-1-propanol), and (1-(3-aminopropyl)-4-methylpiperazine-end-modified poly(1,5 pentanediol diacrylate-co-3-amino-1-propanol).

Array Substrates

In some embodiments, the sensor array comprises a substrate. Regardless of the identity of the sensor element, this invention can be embodied by a matrix of sensor elements immobilized on, connected with and/or coupled to a solid substrate. The substrate may comprise, consist essentially of or consist of polydimethylsiloxane (PDMS), silica, gold or gold coated substrate, silver or silver coated substrate, platinum or platinum coated substrate, zinc or zinc coated substrate, carbon coated substrate and the like. One skilled in the art would be able to select an appropriate substrate for the sensor array. In some embodiments, the sensor elements and the substrate are made of the same element, for example, gold. In some embodiments, the substrate and sensor elements (e.g. nanoparticles) form a chip.

In some embodiments, the plurality of sensor elements comprises a single surface, plate or chip containing two or more discrete sensor elements (regions) with topological differences that allows for discrete biomolecule corona formation at each discrete element (region). The surface plate or chip may be fabricated to include the two or more discrete elements (regions) by the methods described herein. The discrete regions may be raised surfaces of differing geometric shapes, differing sizes or differing charges or other topological differences that result in discrete sensor elements with ability to form discrete biomolecule coronas.

In some embodiments, the sensor elements are non-covalently attached to the substrate. Suitable methods of non-covalent attachment are known in the art and include, but are not limited to, for example, metal coordination, charge interaction, hydrophobic-hydrophobic interaction, chelation and the like. In other embodiments, the sensor elements are covalently attached to the substrate. Suitable methods of covalently linking the sensor elements and the substrates include, but are not limited to, for example, click chemistry, irradiation, and the like.

For purposes of illustration only, methods of attaching the sensor elements, e.g. nanoscale sensor elements, to substrates is demonstrated in FIGS. 23-40 . For example, sensor elements may be conjugated to a substrate (e.g. silica substrate) via the amidation reaction between the amino groups on silica substrate surface and carboxylic acid groups on nanoparticle surface (FIG. 23 ), via the ring-opening reaction between the epoxy groups on silica substrate surface and amino groups on nanoparticle surface (FIG. 24 ), via the Michael Addition reaction between the maleimide groups on silica substrate surface and thiol or amino groups on nanoparticle surface (FIG. 25 ), via the urethane reaction between the isocyanate groups on silica substrate surface and hydroxyl or amino groups on nanoparticle surface (FIG. 26 ), via the oxidation reaction between the thiol groups on silica substrate surface and the ones on nanoparticle surface (FIG. 27 ), via the “Click” chemistry between azide groups on silica substrate surface and alkyne groups on nanoparticle surface (FIG. 28 ), via the thiol exchange reaction between 2-pyridyldithiol groups on silica substrate surface and thiol groups on nanoparticle surface (FIG. 29 ), via the coordination reaction between boronic acid groups on silica substrate surface and diol groups on nanoparticle surface (FIG. 30 ), via the UV light-irradiated addition reaction between C═C bonds on substrate surface and C═C bonds on nanoparticle surface (FIG. 31 ) and the like. Suitable methods of conjugating sensor elements to gold substrate are known in the art and include, for example, conjugation via Au-thiol bonds (FIG. 32 ), via the amidation reaction between the carboxylic acid groups on gold substrate surface and the amino groups on nanoparticle surface (FIG. 33 ), via “Click” chemistry between the azide groups on gold substrate surface and the alkyne groups on nanoparticle surface (FIG. 34 ), via urethane reaction between the NHS groups on gold substrate surface and the amino groups on nanoparticle surface (FIG. 35 ), via the ring-opening reaction between the epoxy groups on gold substrate surface and amino groups on nanoparticle surface (FIG. 36 ), via the coordination reaction between boronic acid groups on silica substrate surface and diol groups on nanoparticle surface (FIG. 37 ), via the UV light-irradiated addition reaction between C═C bonds on gold substrate surface and C═C bonds on nanoparticle surface (FIG. 38 ), via the “Ligand-Receptor” interaction between biotin on gold substrate surface and avidin on nanoparticle surface (FIG. 39 ), via the “Host-Guest” interaction between a-cyclodextrin (a-CD) on gold substrate surface and adamantine (Ad) on nanoparticle surface (FIG. 40 ), and the like.

In another example, so-called “click chemistry” can be used to attach the functional surface groups to the core structures of the nanoparticles (see, e.g., the Sigma Aldrich catalog and U.S. Pat. No. 7,375,234, which are both incorporated herein by reference in their entireties). Of the reactions comprising the click chemistry field, one example is the Huisgen 1,3-dipolar cycloaddition of alkynes to azides to form 1,4-disubsituted-1,2,3-triazoles. The copper (I)-catalyzed reaction is mild and very efficient, requiring no protecting groups, and requiring no purification in many cases. The azide and alkyne functional groups are generally inert to biological molecules and aqueous environments. The triazole has similarities to the ubiquitous amide moiety found in nature, but unlike amides, is not susceptible to cleavage. Additionally, they are nearly impossible to oxidize or reduce.

The plurality of sensor elements may be attached to the substrate randomly or in a distinct pattern. The sensor elements may be substantially uniformly positioned. The pattern of the arranged sensor elements may vary according to the pattern in which the sensor elements are attached to the substrate. Each sensor element is separated by a distance. The distance between the sensor elements (e.g. nanoparticles) arranged on the substrate may vary depending on the length of the linker used to attach or other fabrication conditions. According to various embodiments, the plurality of sensor elements on the array can be fabricated having a desired inter-element distance and pattern. Suitable distinct patterns are known in the art, including, but not limited to, parallel lines, squares, circles, triangles and the like. Further, the sensor elements may be arranged in rows, or columns. In some embodiments, the substrate is a flat substrate, in other embodiments, the substrate is in the form of microchannels or nanochannels. For illustrative purposes only, suitable embodiments are described in FIG. 15-22 . The sensor elements may be contained within microchannels or nanochannels that restrict or control the flow of the sample through the sensor array. Suitable microchannels can range from 10 μm to about 100 μm in size.

In some embodiments, non-limiting examples of the plurality of sensor elements include, but are not limited to, (a) a plurality of sensor elements made of the same material but differing in physiochemical properties, (b) a plurality of sensor elements where one or more sensor element is made of a different material with the same or differing physiochemical properties, (c) a plurality of sensor elements made of the same material differing in size, (d) a plurality of sensor elements made of different material with relatively the same size; (e) a plurality of sensor elements made of different material and made of different sizes, (f) a plurality of sensor elements in which each element is made of a different material, (g) a plurality of sensor elements having different charges, among others. The plurality of sensor elements can be in any suitable combination of two or more sensor elements in which each sensor element provides a unique biomolecule corona signature. For example, the plurality of sensor elements may include one or more liposome and one or more nanoparticle described herein. In one embodiment, the plurality of sensor elements can be a plurality of liposomes with varying lipid content and/or varying charges (cationic/anionic/neutral). In another embodiment, the plurality of sensors may contain one or more nanoparticle made of the same material but of varying sizes and physiochemical properties. In another embodiment, the plurality of sensors may contain one or more nanoparticle made of differing materials (e.g. silica and polystyrene) with similar or varying sizes and/or physiochemical properties (e.g. modifications, for example, —NH₂, —COOH functionalization). These combinations are purely provided as examples and are non-limiting to the scope of the invention.

The angle of curvature on the surface of the particles can change depending on the size of the particles. This change in angle of curvature in turn changes the surface area to which proteins may attach and interact with each other on the particles. As shown in FIG. 58 , increasing the size of the particle results in a change in the amount of protein bound and also in the pattern of proteins attached to the different sized nanoparticles (in this example, the SDS-PAGE analysis of proteins on nanoparticles of diameters of 0.1 μm, 3 μm and 4 μm are shown).

The novelty of the sensor array is it not only can detect different proteins between the different sensor elements, but the ability to compare the levels of the same protein between the different sensor elements. For example, not to be bound by any theory but in order to illustrate the uniqueness of the present sensory array, a theoretical example is described. In some embodiments, the sample is contacted with a first sensor element A, a second sensor element B, and a third sensor element C, wherein each sensor element produces a distant protein corona signature (i.e., A′, B′ and C′). The compositions of each protein corona signature A′, B′ and C′ can be different from one another. In some embodiments, A′ B′ and C′ can comprise the same protein but in a different amount, which can provide additional proteomic information not obtainable by characterizing the sample with previously known approaches. In other words, each unique corona protein information from each nanoparticle serves as unique variables, and therefore provides more data proteomics data. For example, albumin may be found in the protein corona signature of only one sensor element A, in the signature of two sensors, e.g. A and B, B and C or A and C, or in all three sensor biomolecule signatures (A, B, C). Further, the sensor array does not just determine the presence or absence of the protein, e.g., albumin, but it also can determine the comparison of the amount of the protein from one sensor to the other. For example, albumin may be found at concentration X in the signature of A, the concentration of 1/3× in sensor B and at a concentration of 2× in sensor C for a specific biomolecule fingerprint. In another biomolecule fingerprint, the same protein, albumin, could be found in 3 different concentrations, for example, 1/8× in sensor D, 3× in sensor E and 1/4× in sensor F. Thus, a plurality of sensors gives not only a data point for the concentration of a protein, but there can be a comparison of the concentration of the protein between two or more sensors. Further, the concentration or rare or low-abundant proteins can be compared to the concentration of a known protein providing further data regarding the protein coronas. For example, for illustrative purposes, the concentration of an unknown protein, e.g. protein Z, may be compared to the amount of a known protein, e.g. albumin in the different biomolecule coronas. For example, Z may be found at a ratio to albumin of 1:8 on sensor A, 1:50 on sensor B, and not present on sensor C. FIG. 12 provides an analysis of the comparison of rare proteins to albumin concentration within protein coronas analyzed. Thus, statistical analysis can take both the presence of a protein, the relative concentration between each sensor element, and the concentration of a rare or low-abundant protein as compared to a known protein of a particular concentration when analyzing the data.

In some embodiments, a channel is formed by lithography, etching, embossing, or molding of a polymeric surface. In general, the fabrication process may involve one or more of any of these processes, and different parts of the array may be fabricated using different methods and assembled or bonded together.

Lithography involves use of light or other form of energy such as electron beam to change a material. Typically, a polymeric material or precursor (e.g. photoresist, a light-resistant material) is coated on a substrate and is selectively exposed to light or other form of energy. Depending on the photoresist, exposed regions of the photoresist either remain or are dissolved in subsequent processing steps known generally as “developing.” This process results in a pattern of the photoresist on the substrate. In some embodiments, the photoresist is used as a master in a molding process. In some embodiments, a polymeric precursor is poured on the substrate with photoresist, polymerized (i.e. cured) and peeled off.

In some embodiments, the photoresist is used as a mask for an etching process. For example, after patterning photoresist on a silicon substrate, channels can be etched into the substrate using a deep reactive ion etch (DRIE) process or other chemical etching process known in the art (e.g. plasma etch, KOH etch, HF etch, etc.). The photoresist is removed, and the substrate is bonded to another substrate using one of any bonding procedures known in the art (e.g. anodic bonding, adhesive bonding, direct bonding, eutectic bonding, etc.). Multiple lithographic and etching steps and machining steps such as drilling may be included as required.

In some embodiments, a polymeric substrate may be heated and pressed against a master mold for an embossing process. The master mold may be formed by a variety of processes, including lithography and machining. The polymeric substrate is then bonded with another substrate to form channels and/or a mixing apparatus. Machining processes may be included if necessary.

In some embodiments, a molten polymer or metal or alloy is injected into a suitable mold and allowed to cool and solidify for an injection molding process. The mold typically consists of two parts that allow the molded component to be removed. Parts thus manufactured may be bonded to result in the substrate.

In some embodiments, sacrificial etch may be used to form channels. Lithographic techniques may be used to pattern a material on a substrate. This material is covered by another material of different chemical nature. This material may undergo lithography and etch processes, or other machining process. The substrate is then exposed to a chemical agent that selectively removes the first material. Channels are formed in the second material, leaving voids where the first material was present before the etch process.

In some embodiments, microchannels are directly machined into a substrate by laser machining or CNC machining. Several layers thus machined may be bonded together to obtain the final substrate.

In some embodiments, the width or height of each channel ranges from approximately 1 μm to approximately 1000 μm. In some embodiments, the width or height of each channel ranges from approximately 5 μm to approximately 500 μm. In some embodiments, the width or height of each channel ranges from approximately 10 μm to approximately 100 μm. In some embodiments, the width or height of each channel a ranges from approximately 25 μm to approximately 100 μm. In some embodiments, the width or height of each channel ranges from approximately 50 μm to approximately 100 μm. In some embodiments, the width or height of each channel ranges from approximately 75 μm to approximately 100 μm. In some embodiments, the width or height of each channel ranges from approximately 10 μm to approximately 75 μm. In some embodiments, the width or height of each channel ranges from approximately 10 μm to approximately 50 μm. In some embodiments, the width or height of each channel ranges from approximately 10 μm to approximately 25 μm.

In some embodiments, the maximum width or height of a channel is approximately 1 μm, approximately 5 μm, approximately 10 μm, approximately 20 μm, approximately 30 μm, approximately 40 μm, approximately 50 μm, approximately 60 μm, approximately 70 μm, approximately 80 μm, approximately 90 μm, approximately 100 μm, approximately 250 μm, approximately 500 μm, or approximately 1000 μm.

In some embodiments, the width of each channel ranges from approximately 5 μm to approximately 100 μm. In some embodiments, the width of a channel is approximately 5 μm, approximately 10 μm, approximately 15 μm, approximately 20 μm, approximately 25 μm, approximately 30 μm, approximately 35 μm, approximately 40 μm, approximately 45 μm, approximately 50 μm, approximately 60 μm, approximately 70 μm, approximately 80 μm, approximately 90 μm, or approximately 100 μm.

In some embodiments, the height of each channel ranges from approximately 10 μm to approximately 1000 μm. In some embodiments, the height of a channel is approximately 10 μm, approximately 100 μm, approximately 250 μm, approximately 400 μm, approximately 500 μm, approximately 600 μm, approximately 750 μm, or approximately 1000 μm. In specific embodiments, the height of the channel(s) through which the sample flows is approximately 500 μm. In specific embodiments, the height of the channel(s) through which the sample flows is approximately 500 μm.

In some embodiments, the length of each channel ranges from approximately 100 μm to approximately 10 cm. In some embodiments, the length of a channel is approximately 100 μm, approximately 1.0 mm, approximately 10 mm, approximately 100 mm, approximately 500 mm, approximately 600 mm, approximately 700 mm, approximately 800 mm, approximately 900 mm, approximately 1.0 cm, approximately 1.1 cm, approximately 1.2 cm, approximately 1.3 cm, approximately 1.4 cm, approximately 1.5 cm, approximately 5 cm, or approximately 10 cm. In specific embodiments, the length of the channel(s) through which the sample flows is approximately 1.0 cm. In specific embodiments, the length of the channel(s) through which the sample flows is approximately 1.0 cm.

Biomolecule Corona Nanosystem

Provided herein is biomolecule corona nanosystem or sensor arrays comprising, consisting essentially of or consists of a plurality of sensor elements wherein the plurality of sensor elements differ from each other in at least one physiocochemical property. In some embodiments, a plurality of sensor elements are a plurality of nanoparticles. In some embodiments, a plurality of nanoparticles are a plurality of liposomes. In some embodiments, each sensor element is able to bind a plurality of biomolecules in a complex biological sample to produce a biomolecule corona signature. In some embodiments, each sensor elements has a distinct biomolecule corona signature.

The biomolecule corona signature refers to the composition, signature or pattern of different biomolecules that are bound to each separate sensor element or each nanoparticle. In some cases, the biomolecule corona signature is a protein corona signature. In another case, the biomolecule corona signature is a polysaccharide corona signature. In yet another case, the biomolecule corona signature is a metabolite corona signature. In some cases, the biomolecule corona signature is a lipidomic corona signature. The signature not only refers to the different biomolecules but also the differences in the amount, level or quantity of the biomolecule bound to the sensor element or the nanoparticle, or differences in the conformational state of the biomolecule that is bound to the sensor element or the nanoparticle. It is contemplated that the biomolecule corona signatures of each sensor elements may contain some of the same biomolecules, may contain distinct biomolecules with regard to the other sensor elements or nanoparticles, and/or may differ in level or quantity, type or confirmation of the biomolecule. The biomolecule corona signature may depend on not only the physiocochemical properties of the sensor element or the nanoparticle, but also the nature of the sample and the duration of exposure. In some embodiments, the biomolecule corona signature comprises the biomolecules found in a soft corona and a hard corona.

In some embodiments, the sensor array comprises, consists essentially of or consists of a first sensor element that produces a first biomolecule corona signature and at least one second sensor element or at least one nanoparticle that produces at least one second biomolecule corona signature when the sensor array is contacted with a complex biological sample. A biomolecule fingerprint is the combination of the first biomolecule signature and the at least one second biomolecule signature. It is contemplated that the biomolecule signature can be made from at least two biomolecule corona signatures to as many different biomolecule signatures are assayed, e.g. at least 1000 different biomolecule corona signatures. The biomolecule corona can be assayed separately for each sensor element to determine the biomolecule corona signature for each element each nanoparticle, or each liposome and combined to determine the biomolecule fingerprint or the two or more biomolecule corona can be assayed at the same time to develop the biomolecule fingerprint at once.

The biomolecule fingerprint can distinguish between different possible biological states (e.g., disease states) of a subject. In some embodiments, the biomolecule fingerprint is associated with the development of a disease or disorder and/or is able associated with a disease state of the subject.

In some embodiments, the biomolecule fingerprint is able to determine a disease state for a subject. The term “disease state” for a subject as used herein refers to the ability of sensor array of the present technology to be able to differentiate between the different states of a disease within a subject. This term encompasses a pre-disease state or precursor state of a disease or disorder (a state in which the subject may not have any outward signs or symptoms of the disease or disorder but will develop the disease or disorder in the future) and a disease state in which the subject has a stage of the disease or disorder (e.g., an early, intermediate or late stage of the disease or disorder). In other words, the disease state is a spectrum that encompasses a continuum regarding the health of a subject with respect to a disease or disorder. The array of the present invention is able to distinguish different diseases states for a subject by determining a biomolecule fingerprint which can be compared to differing biomolecule fingerprints that are associated with different disease states on the spectrum and to healthy subjects. In another example, the biomolecule fingerprint may be associated with a pre-disease state or precursor disease state, in which the subject appears healthy at the time with no outward signs or symptoms of a disease, but will develop the disease in the future. In another example, the biomolecule fingerprint may indicate that the subject has the disease, and is able to distinguish if the disease is in the early, intermediate or late stages by the unique biomolecule fingerprint associated with each stage.

As discussed above, the disease state also includes a precursor state of a disease or disorder. This precursor state is a state in which the subject does not have any outward signs or symptoms of the disease or disorder (although there may be submacro changes within the biomolecules of the subject found in their blood or other biological fluids) but will develop the disease or disorder in the future. This precursor state can also be described as a state in which the first pathological changes of a disease are seen, e.g. changes in the biomolecule fingerprint of a biological sample from the patient.

Another example of a biological state is a healthy, non-disease state. The array can also determine a specific biomolecule fingerprint associated with a healthy, non-disease state, where the subject will not develop the disease in the future. In this case, the subject has no evidence at the time of the test that they either have the disease or will develop the disease in the future.

Herein the term “biological state” encompasses any biological characteristic of a subject which can be manifested in a biological sample as defined herein. A biological state can be detected using the methods disclosed herein where two subjects who differ in the biological state manifest those differences in the composition of a sample. For example, a biological state includes a disease state of a subject. A disease state can be detected when the disease state gives rise to changes in the molecular composition (e.g., level of one or more proteins) of a sample of a subject expressing the disease state relative to a sample of a subject not having the disease state (i.e., where the biological state is a healthy state or non-disease state).

Another example of a biological state is a level of responsiveness of a subject to a particular therapeutic treatment (e.g. administration of one or a combination of drugs or pharmaceuticals). In some embodiments, a biological state is responsiveness (e.g., with respect to a particular threshold of analysis) of a subject to a particular drug. In another embodiment, a biological state is non-responsiveness (e.g., with respect to a particular threshold of analysis) of a subject to a particular drug. In some embodiments, the level of responsiveness of a subject to a drug (i.e., biological state of responsiveness to the drug or biological state of non-responsiveness to the drug) is associated with factors such as variability in metabolism or pharmacokinetics of the drug between subjects.

Another example of a biological state is the level of immune response exhibited by a subject. In some embodiments, the biological state can be increased immune response. In other embodiments, the biological state can be decreased immune response. Immune response can differ between subjects as a result of a number of variables. For example, immune response can differ between subjects as a result of differing exposure to an exogenously introduced antigen (e.g. associated with a virus or bacteria), as a result of differences in their susceptibility to an autoimmune disease or disorder, or secondarily as a result of a response to other biological states in a subject (e.g., disease states such as cancer).

Other examples of biological states that can be associated with a biomolecule fingerprint include susceptibility of a subject to adverse effects associated with administration of a drug, and identification of a subject's potential to exhibit an allergic reaction to administration of a particular composition or substance.

The innovation in this sensor arrays and associated methods differ from the current methods of detecting or measuring the presence or absence or levels of certain biomarkers to predict if a subject may have a pre-disposition or likelihood of developing a disease or disorder at a very early stages of the disease, before any signs or symptoms can be monitored can be assayed. Suitably, the array is able to differentiate the health of the subject from no disease or disorder, having a precursor of a disease or disorder, and having the disease or disorder. However, the invention is not limited to those embodiments and covers the spectrum of other disease states that may occur within the continuum of health and disease of a subject.

Further, the innovation of the present invention sensor arrays can be demonstrated by the following examples. The sensor array of the present invention is very sensitive and able to detect not only changes in small amounts of biomolecules within a sample, but rely on the interactions between the biomolecules. For example, not to be bound by any theory but in order to illustrate the uniqueness of the present sensory array, a theoretical example is described. If, for example, biological samples are collected from a subject over time (e.g., before any signs and symptoms of the disease, pre-disease state and during early and intermediate stages of a disease). In these samples, by just measuring a level of a biomolecule X in the sample (e.g. quantitation of amount) it may be found that the concentration does not alter over the different disease states. Thus, measuring biomolecule X would not be a useful marker for the disease However, using the present sensor array, although the level of biomarker X may be the same, the interaction of biomolecule X with other biomolecules, Y and Z, may change the composition of the protein corona signature associated with the sample over time and samples. For example, biomarker X may change its association from associating with biomolecule Y to biomolecule Z, or over time interaction of X with Y and Z leads to a conformational change in X. This type of changes, that does not change the overall concentration but will change the unique biomolecule fingerprint associated with the disease state (that includes biomolecule X) would allow for the distinction and association with other disease states. This would not be discovered if you use methods of the art of just measuring the quantitation of biomolecule X within the sample, as this level stayed the same throughout the entire disease. This is an unexpectedly highly specific and useful assay not seen before. With this assay, biomarkers of a disease that would not previously been characterized as biomarkers can be determined including, patterns of biomarkers, as these marker may not change in absolute amounts within the samples, but will have a consistent and measurable change with regard to the interaction with the sensor elements in the sensor array. The ability to distinguish patterns by analysis of the biomolecule corona allows for the ability to associate these patterns with different disease states.

As discussed above, the present sensor array has the ability to detect proteins over ten order of magnitude, which is a higher sensitivity than any previously described methods. The uniqueness of the present sensor array is found in the ability of the array to detect proteins regardless of the level of concentration within the sample. The assay relies on the ability of the biomolecule (e.g. protein), known or unknown, within the sample to interact with the sensor elements, and to interact differently and at different amounts with different sensor elements and also to interact with the other biomolecules associated with the sensor element. This in turn, allows for there to be the ability to detect low-abundance and rare proteins even in the presence of high abundant proteins (such as albumin) within the sample. As demonstrated in FIG. 12 of Example 1, the ability of the senor array to detect concentrations over 10 order of magnitude even in the presence of high abundant proteins has been shown. Further, the sensor array is also able to detect proteins with unknown/unreported plasma concentrations, which previously have not been found with current methods. One unique feature among others of the present sensor array is the ability of the present system to be able to detect low-abundant proteins and rare proteins. The present sensor array can be used to not only determine a disease state (no disease, pre-disease, or early and late stage disease) but in some cases to distinguish between subtypes of diseases (e.g. distinguish between different types of cancer, e.g. lung cancer, breast cancer, myeloma, etc).

Detection Methods

The present sensor array may be used in a variety of methods described herein. The ability to determine a unique biomolecule fingerprint for samples provides a novel and innovative means to measure a specific disease state in a subject. These biomolecule fingerprints can be used to determine the disease state of a subject, diagnosing or prognosing a disease in a subject or identifying unique patterns of biomarkers that are associated with a disease state or a disease or disorder. For example, the changes in the biomolecule fingerprint in a subject over time (days, months, years) allows for the ability to track a disease or disorder in a subject (e.g. disease state) which may be broadly applicable to determination of a biomolecule fingerprint that can be associated with the early stage of a disease or any other disease state. As discussed above, the ability to detect a disease early on, for example cancer, even before it fully develops or metastasizes allows for a significant increase in positive outcomes for those patients and the ability to increase life expectancy and lower mortality associated with that disease. Therefore, the sensor array of the present invention provides a unique opportunity to be able to develop biomolecule fingerprints associated with the pre-stages or precursor states of the disease.

It is understood that even before a disease has progressed into showing any measurable signs or symptoms, that at the macroscopic level, there are changes taking place within the body and biological systems of a subject. Being able to recognize these early pre-disease signs contemplated by use of the sensor array of the present invention. The inventors have found that by comparing the biomolecule fingerprint of a subject during different times of a disease state (e.g. before a disease has shown symptoms and developed, after early signs or symptoms of the disease, and/or at late stages of the disease) provides a unique biomolecule fingerprint linked to the different disease states linked to the disease progression. In other words, a biomolecule fingerprint can be determined that would allow one to be able to identify subjects that are going to develop a disease at a later time. This would allow for early monitoring and early treatment, greatly improving the outcome of the subject diagnosed with the disease.

In some embodiments, a method of detecting a disease or disorder in a subject are provided. The method comprises the steps of (a) obtaining a sample from the subject; (b) contacting the sample with a sensor array as described herein, and (c) determining a biomolecule fingerprint associated with the sample, wherein the biomolecule fingerprint differentiates the health of subject in a disease state, for example, from no disease or disorder, having a precursor of a disease or disorder, and having disease or disorder.

The step of determining a biomolecule fingerprint associated with the sample may comprise detecting the biomolecule corona signature for at least two sensor elements, wherein the combination of the at least two biomolecule corona signatures produces the biomolecule fingerprint. In some embodiments, the biomolecule corona signatures of the at least two sensor elements are assayed separately and the results combined to determine the biomolecule fingerprint. In some embodiments the biomolecule corona signatures of the at least two elements are assayed at the same time or in the same sample.

In some embodiments, the method of determining the biomolecule fingerprint comprises detecting and determining the biomolecular corona signatures of the at least two sensor elements. In some embodiments, this step can be done by separating the plurality of biomolecules attached to each sensor element (e.g. separating the biomolecule corona from the sensor element) and assaying the plurality of biomolecules to determine the composition of the plurality of biomolecule coronas to determine a biomolecule fingerprint. Depending on the design of the array, in some instances the composition of each biomolecule corona signature of each sensor element is assayed independently, and the results are combined to produce the biomolecule fingerprint (e.g. each sensor element is in a separate channel or compartment wherein the specific composition of the biomolecule corona for that specific sensor element can be separately analyzed (e.g. either by detaching the biomolecules and assaying by mass spectrometry and/or chromatography or by detecting the plurality of biomolecules still attached to the sensor element by fluorescence, luminescence or other means). In another embodiment, the at least two sensor elements are on the same array and the composition of the biomolecule corona for the at least two sensor elements is assayed at the same time by dissociating the biomolecule corona from both sensor elements into one solution and assaying that solution to determining a biomolecule signature. This later method would be the method of choice if using a chip array technology.

Methods of assaying the plurality of biomolecules that make up the biomolecule corona signature or the biomolecule fingerprint are known in the art and include, but are not limited to, for example, gel-electrophoresis, liquid chromatography, mass spectrometry, nuclear magnetic resonance spectroscopy (NMR), fourier transform infrared spectroscopy (FTIR), circular dichroism, Raman spectrometry, and a combination thereof. In a preferred embodiment, the assay is by liquid chromatography, mass spectrometry or a combination thereof.

In a preferred embodiment, the sensor assay is a non-label array.

In some embodiments, it is contemplated that labelled arrays may be used, wherein a corona signature is able to be determined as a change is signal (e.g. fluorescence, luminescence, charge, colormetric dyes). Suitable example is shown in FIGS. 42 and 43 . For example, an array may include chemically responsive colorants in a formulation for detection and identification of biomolecules based on the equilibrium interactions with the biomolecules and responsive dyes.

In some embodiments, the sensor element comprises a complex with a first component and a polymer fluorophore or other quencher component chemically complementary to the first component where such a complex having an initial background or reference fluorescence. Once the first component comes into contact with the biomolecule corona, it will affect the quenching of the fluorophore and this change in fluorescence can be measured. After the sensor is irradiated and/or excited with a laser, the effect and/or change in fluorescence for each sensor element can be measured and compared to the background fluorescence to produce the biomolecule fingerprint.

The sensor arrays and methods described herein can be used to determine a disease state, and/or prognose or diagnose a disease or disorder. The diseases or disorders contemplated include, but are not limited to, for example, cancer, cardiovascular disease, endocrine disease, inflammatory disease, a neurological disease and the like.

In one embodiment, the disease or disorder is cancer. In suitable embodiments, the sensor array and methods described herein is not only able to diagnose cancer (e.g. determine if a subject (a) does not have cancer, (b) is in a pre-cancer development stage, (c) is in early stage of cancer, (d) is in a late stage of cancer) but in some embodiments is able to determine the type of cancer. As demonstrated in the examples below, a sensor array comprising six sensor elements was able to accurately determine the disease state of the presence or absence of cancer. Additionally, the Examples demonstrate that a sensor array comprising six sensor elements was able to distinguish between different cancer types (e.g. lung cancer, glioblastoma, meningioma, myeloma and pancreatic cancer).

The term “cancer” and “tumor” as used herein interchangeably and are meant to encompass any cancer, neoplastic and preneoplastic disease that is characterized by abnormal growth of cells. Cancer may, for example, be selected from the group consisting of lung cancer, pancreas cancer, myeloma, myeloid leukemia, meningioma, glioblastoma, breast cancer, esophageal squamous cell carcinoma, gastric adenocarcinoma, prostate cancer, bladder cancer, ovarian cancer, thyroid cancer, neuroendocrine cancer, colon carcinoma, ovarian cancer, head and neck cancer, Hodgkin's Disease, non-Hodgkin's lymphomas, rectum cancer, urinary cancers, uterine cancers, oral cancers, skin cancers, stomach cancer, brain tumors, liver cancer, laryngeal cancer, esophageal cancer, mammary tumors, fibrosarcoma, myxosarcoma, liposarcoma, chondrosarcoma, osteogenic sarcoma, chordoma, angiosarcoma, endotheliosarcoma, Ewing's sarcoma, squamous cell carcinoma, basal cell carcinoma, adenocarcinoma, sweat gland carcinoma, sebaceous gland carcinoma, papillary carcinoma, papillary adenocarcinomas, cystandeocarcinoma, medullary carcinoma, bronchogenic carcinoma, renal cell carcinoma, hepatoma, bile duct carcinoma, choriocarcinoma, seminoma, embryonal carcinoma, Wilms' tumor, cervical cancer, testicular tumor, endometrial cancer, lung carcinoma, small cell lung carcinoma, bladder carcinoma, epithelial carcinoma, glioblastomas, neuronomas, craniopharingiomas, schwannomas, glioma, astrocytoma, meningioma, melanoma, neuroblastoma, retinoblastoma, leukemias and lymphomas, acute lymphocytic leukemia and acute myelocytic polycythemia vera, multiple myeloma, Waldenstrom's macroglobulinemia, and heavy chain disease, acute nonlymphocytic leukemias, chronic lymphocytic leukemia, chronic myelogenous leukemia, childhood-null acute lymphoid leukemia (ALL), thymic ALL, B-cell ALL, acute megakaryocytic leukemia, Burkitt's lymphoma, and T cell leukemia, small and large non-small cell lung carcinoma, acute granulocytic leukemia, germ cell tumors, endometrial cancer, gastric cancer, hairy cell leukemia, thyroid cancer and other cancers known in the art. In a preferred embodiment, the cancer is selected from the group consisting of lung cancer, pancreas cancer, myeloma, myeloid leukemia, meningioma, glioblastoma, breast cancer, esophageal squamous cell carcinoma, gastric adenocarcinoma, prostate cancer, bladder cancer, ovarian cancer, thyroid cancer, and neuroendocrine cancer.

As used herein, the terms “cardiovascular disease” (CVD) or “cardiovascular disorder” are used to classify numerous conditions affecting the heart, heart valves, and vasculature (e.g., veins and arteries) of the body and encompasses diseases and conditions including, but not limited to atherosclerosis, myocardial infarction, acute coronary syndrome, angina, congestive heart failure, aortic aneurysm, aortic dissection, iliac or femoral aneurysm, pulmonary embolism, atrial fibrillation, stroke, transient ischemic attack, systolic dysfunction, diastolic dysfunction, myocarditis, atrial tachycardia, ventricular fibrillation, endocarditis, peripheral vascular disease, and coronary artery disease (CAD). Further, the term cardiovascular disease refers to subjects that ultimately have a cardiovascular event or cardiovascular complication, referring to the manifestation of an adverse condition in a subject brought on by cardiovascular disease, such as sudden cardiac death or acute coronary syndrome, including, but not limited to, myocardial infarction, unstable angina, aneurysm, stroke, heart failure, non-fatal myocardial infarction, stroke, angina pectoris, transient ischemic attacks, aortic aneurysm, aortic dissection, cardiomyopathy, abnormal cardiac catheterization, abnormal cardiac imaging, stent or graft revascularization, risk of experiencing an abnormal stress test, risk of experiencing abnormal myocardial perfusion, and death.

As used herein, the ability to detect, diagnose or prognose cardiovascular disease, for example, atherosclerosis, can include determining if the patient is in a pre-stage of cardiovascular disease, has developed early, moderate or severe forms of cardiovascular disease, or has suffered one or more cardiovascular event or complication associated with cardiovascular disease.

Atherosclerosis (also known as arteriosclerotic vascular disease or ASVD) is a cardiovascular disease in which an artery-wall thickens as a result of invasion and accumulation and deposition of arterial plaques containing white blood cells on the innermost layer of the walls of arteries resulting in the narrowing and hardening of the arteries. The arterial plaque is an accumulation of macrophage cells or debris, and contains lipids (cholesterol and fatty acids), calcium and a variable amount of fibrous connective tissue. Diseases associated with atherosclerosis include, but are not limited to, atherothrombosis, coronary heart disease, deep venous thrombosis, carotid artery disease, angina pectoris, peripheral arterial disease, chronic kidney disease, acute coronary syndrome, vascular stenosis, myocardial infarction, aneurysm or stroke.

For illustrative purposes, in one embodiment the sensor arrays may distinguish the different stages of atherosclerosis, including, but not limited to, the different degrees of stenosis in a subject.

Further, for illustrative purposes only, the examples below demonstrate the use of a sensor array to detect the different state of coronary artery disease. A sensor array containing six sensor elements was able to distinguish subjects with CAD as diagnosed by coronary angiography, patients with symptoms that had healthy coronary vessels (NO CAD), patients with restenosis (reoccurrence of CAD after treatment) and healthy subjects with no risk factors (FIG. 53 ). The present sensor array was sensitive enough to detect the difference between people who ad symptoms of coronary artery disease but did not have stenosis of the arteries (e.g. NO CAD vs CAD groups). This provides a novel diagnostic CAD test that can be used as a non-invasive screening for at risk patients.

The term “endocrine disease” is used to refer to a disorder associated with dysregulation of endocrine system of a subject. Endocrine diseases may result from a gland producing too much or too little of an endocrine hormone causing a hormonal imbalance, or due to the development of lesions (such as nodules or tumors) in the endocrine system, which may or may not affect hormone levels. Suitable endocrine diseases able to be treated include, but are not limited to, e.g., Acromegaly, Addison's Disease, Adrenal Cancer, Adrenal Disorders, Anaplastic Thyroid Cancer, Cushing's Syndrome, De Quervain's Thyroiditis, Diabetes, Follicular Thyroid Cancer, Gestational Diabetes, Goiters, Graves' Disease, Growth Disorders, Growth Hormone Deficiency, Hashimoto's Thyroiditis, Hurthle Cell Thyroid Cancer, Hyperglycemia, Hyperparathyroidism, Hyperthyroidism, Hypoglycemia, Hypoparathyroidism, Hypothyroidism, Low Testosterone, Medullary Thyroid Cancer, MEN 1, MEN 2A, MEN 2B, Menopause, Metabolic Syndrome, Obesity, Osteoporosis, Papillary Thyroid Cancer, Parathyroid Diseases, Pheochromocytoma, Pituitary Disorders, Pituitary Tumors, Polycystic Ovary Syndrome, Prediabetes, Silent, Thyroiditis, Thyroid Cancer, Thyroid Diseases, Thyroid Nodules, Thyroiditis, Turner Syndrome, Type 1 Diabetes, Type 2 Diabetes, and the like.

As referred to herein, inflammatory disease refers to a disease caused by uncontrolled inflammation in the body of a subject. Inflammation is a biological response of the subject to a harmful stimulus which may be external or internal such as pathogens, necrosed cells and tissues, irritants etc. However, when the inflammatory response becomes abnormal, it results in self-tissue injury and may lead to various diseases and disorders. Inflammatory diseases can include, but are not limited to, asthma, glomerulonephritis, inflammatory bowel disease, rheumatoid arthritis, hypersensitivities, pelvic inflammatory disease, autoimmune diseases, arthritis; necrotizing enterocolitis (NEC), gastroenteritis, pelvic inflammatory disease (PID), emphysema, pleurisy, pyelitis, pharyngitis, angina, acne vulgaris, urinary tract infection, appendicitis, bursitis, colitis, cystitis, dermatitis, phlebitis, rhinitis, tendonitis, tonsillitis, vasculitis, autoimmune diseases; celiac disease; chronic prostatitis, hypersensitivities, reperfusion injury; sarcoidosis, transplant rejection, vasculitis, interstitial cystitis, hay fever, periodontitis, atherosclerosis, psoriasis, ankylosing spondylitis, juvenile idiopathic arthritis, Behcet's disease, spondyloarthritis, uveitis, systemic lupus erythematosus, and cancer. For example, the arthritis includes rheumatoid arthritis, psoriatic arthritis, osteoarthritis or juvenile idiopathic arthritis, and the like.

Neurological disorders or neurological diseases are used interchangeably and refer to diseases of the brain, spine and the nerves that connect them. Neurological diseases include, but are not limited to, brain tumors, epilepsy, Parkinson's disease, Alzheimer's disease, ALS, arteriovenous malformation, cerebrovascular disease, brain aneurysms, epilepsy, multiple sclerosis, Peripheral Neuropathy, Post-Herpetic Neuralgia, stroke, frontotemporal dementia, demyelinating disease (including but are not limited to, multiple sclerosis, Devic's disease (i.e. neuromyelitis optica), central pontine myelinolysis, progressive multifocal leukoencephalopathy, leukodystrophies, Guillain-Barre syndrome, progressing inflammatory neuropathy, Charcot-Marie-Tooth disease, chronic inflammatory demyelinating polyneuropathy, and anti-MAG peripheral neuropathy) and the like. Neurological disorders also include immune-mediated neurological disorders (IMNDs), which include diseases with at least one component of the immune system reacts against host proteins present in the central or peripheral nervous system and contributes to disease pathology. IMNDs may include, but are not limited to, demyelinating disease, paraneoplastic neurological syndromes, immune-mediated encephalomyelitis, immune-mediated autonomic neuropathy, myasthenia gravis, autoantibody-associated encephalopathy, and acute disseminated encephalomyelitis.

In a non-limiting example, the Examples below provide a method of diagnosing Alzheimer's in a patient using the sensor array and methods described herein. The sensor array was not only able to accurately distinguish between patients with or without Alzheimer's disease, but was also able to detect patients who were pre-symptomatic and developed Alzheimer's disease several years after the screening (as determined by cohort plasmas). This provides advantages of being able to treat a disease at a very early stage, even before development of the disease.

The sensor arrays and methods of the present invention in some embodiments are able to detect a pre-disease stage of a disease or disorder. A pre-disease stage is a stage at which the patient has not developed any signs or symptoms of the disease. A pre-cancerous stage would be a stage in which cancer or tumor or cancerous cells have not be identified within the subject. A pre-neurological disease stage would be a stage in which a person has not developed one or more symptom of the neurological disease. The ability to diagnose a disease before one or more sign or symptom of the disease is present allows for close monitoring of the subject and the ability to treat the disease at a very early stage, increasing the prospect of being able to halt progression or reduce the severity of the disease.

The sensor arrays and methods of the present invention in some embodiments are able to detect the early stages of a disease or disorder. Early stages of the disease refers to when the first signs or symptoms of a disease may manifest within a subject. Usually diseases able to be caught in either pre-disease development or in the early states are easier to treat and provide a more positive outcome for the patient. For example, for cancer, the early stages of a disease may include stage and stage 1 cancer. Stage 0 cancer describes the cancer in situ, which means “in place” signifying that the cancer is still located in the place it started and have not spread to nearby tissues. This stage of cancer is often highly curable, usually by removing the entire tumor with surgery. Stage 1 cancer is usually a small cancer or tumor that has not grown deeply into nearby tissue and has not spread to lymph nodes or other parts of the body. Further, early stage of a disease may be a stage at which there are no outward signs or symptoms. For example, in Alzheimer's disease an early stage may be a pre-Alzheimer's stage in which no symptoms are detected yet the patient will develop Alzheimer's months or years later.

In some embodiments, the sensor arrays and methods are able to detect intermediate stages of the disease. Intermediate states of the disease describe stages of the disease that have passed the first signs and symptoms and the patient is experiencing one or more symptom of the disease. For example, for cancer, stage II or III cancers are considered intermediate stages, indicating larger cancers or tumors that have grown more deeply into nearby tissue. In some instances, stage II or III cancers may have also spread to lymph nodes but not to other parts of the body.

Further, the sensor arrays and methods are able to detect late or advanced stages of the disease. Late or advanced stages of the disease may also be called “severe” or “advanced” and usually indicates that the subject is suffering from multiple symptoms and effects of the disease. For example, severe stage cancer includes stage IV, where the cancer has spread to other organs or parts of the body and is sometimes referred to as advanced or metastatic cancer.

In some embodiments, the methods of the present technology include comparing the protein fingerprint of the sample to a panel of protein fingerprints associated with a plurality of diseases and/or a plurality of disease states to determine if the sample indicates a disease and/or disease state. For example, samples can be collected from a population of subjects over time. Once the subjects develop a disease or disorder, the present invention allows for the ability to characterize and detect the changes in biomolecule fingerprints over time in the subject by comparing the biomolecule fingerprint of the sample from the same subject before they have developed a disease to the biomolecule fingerprint of the subject after they have developed the disease. In some embodiments, samples can be taken from cohorts of patients who all develop the same disease, allowing for analysis and characterization of the biomolecule fingerprints that are associated with the different stages of the disease for these patients (e.g. from pre-disease to disease states).

For illustrative purposes only, the examples have shown that the methods and sensor arrays of the present invention are able to distinguish not only between different types of cancers, but also between the different stages of the cancer (e.g. early stages of cancer).

Methods of determining a biomolecule fingerprint associated with at least one disease or disorder and/or a disease state are contemplated. The methods comprise the steps of obtaining a sample from at least two subjects diagnosed with the at least one disease or disorder or having the same disease state; contacting each sample with a sensor array described herein to determining a biomolecule fingerprint for each sensor array, and analyzing the fingerprint of the at least two samples to determine a biomolecule fingerprint associated with the at least one disease or disorder and/or disease state.

Classification of Biomolecule Corona

The method of determining the biomolecule fingerprint associated with the disease or disorder and/or disease state include the analysis of the biomolecule fingerprints of the at least two samples. This determination, analysis or statistical classification is done by methods known in the art, including, but not limited to, for example, a wide variety of supervised and unsupervised data analysis, machine learning, deep learning, and clustering approaches including hierarchical cluster analysis (HCA), principal component analysis (PCA), Partial least squares Discriminant Analysis (PLS-DA), random forest, logistic regression, decision trees, support vector machine (SVM), k-nearest neighbors, naive bayes, linear regression, polynomial regression, SVM for regression, K-means clustering, and hidden Markov models, among others. In other words, the biomolecule fingerprint of each sample are compared/analyzed with each other to determine with statistical significance what patterns are common between the individual fingerprints to determine a biomolecule fingerprint that is associated with the disease or disorder or disease state.

Generally, machine learning algorithms are used to construct models that accurately assign class labels to examples based on the input features that describe the example. In some case it may be advantageous to employ machine learning and/or deep learning approaches for the methods described herein. For example, machine learning can be used to associate the biomolecule fingerprint with various disease states (e.g. no disease, precursor to a disease, having early or late stage of the disease, etc.). For example, in some cases, one or more machine learning algorithms are employed in connection with a method of the invention to analyze data detected and obtained by the biomolecule corona and biomolecule fingerprints derived therefrom. For example, in one embodiment, machine learning can be coupled with the sensor array described herein to determine not only if a subject has a pre-stage of cancer, cancer or does not have or develop cancer, but also to distinguish the type of cancer.

The Examples below have shown the ability of the sensor array described herein to determine the disease state for a number of different diseases, including, cancer, cardiovascular disease and neurological disease (e.g. Alzheimer's disease) with statistical significance. This assay is not limited to these specific embodiments, as the sensor array can be applied to a variety of diseases and disease states as described herein.

In some embodiments, the method includes obtaining samples from control subjects which are contacted with the sensor array to produce a control biomolecule fingerprint. These control biomolecule fingerprints can then be used to compare to the biomolecule fingerprints of the subjects with a disease or disorder and/or specific disease state to determine a biomolecule fingerprint specific to that disease or disorder and/or specific disease state.

The method may include, for example, obtaining control sample from at least one control subject, contacting the control sample with the sensor array to produce a plurality of control biomolecule corona, and assaying the plurality of biomolecules of each control biomolecule corona. The method may further comprise comparing the plurality of biomolecules of the plurality of control biomolecule corona with the plurality of biomolecules of the plurality of biomolecule corona from the subject with the disease or disorder to determine a biomolecule fingerprint associated with the at least one disease or disorder.

Methods of diagnosing or prognosing a disease or disorder are also contemplated. The methods comprise obtaining a sample from a subject; contacting the sample with a sensor array to produce a biomolecule fingerprint, and comparing the biomolecule fingerprint to a panel of biomolecule fingerprints associated with a plurality of diseases or disorders; and diagnosing or prognosing the disease or disorder.

In some embodiments, methods of identifying patterns of biomarkers or specific biomarkers associated with a disease or disorder are contemplated. Suitable methods, include, for example, preforming the methods described above (e.g. obtaining a samples from at least two subjects diagnosed with the disease or disorder and at least two control subjects; contacting each sample with the sensor array to produce a biomolecule fingerprint, and comparing the biomolecule fingerprint of the subjects with the disease or disorder to the biomolecule fingerprint of the control subjects to determine at least one pattern and/or biomarker associated with the disease or disorder. Suitable, the method may comprise at least 2 disease subjects and at least two control subjects, alternatively at least 5 disease subjects and at least 5 control subjects, alternatively at least 10 disease subjects and at least 10 control subjects, alternatively at least 15 disease subjects and at least 15 control subjects, alternatively at least 20 disease subjects and at least 20 control subjects, and includes any variations in between (e.g. disease subjects from at least 2-100, and control subjects from at least 2-100).

In some embodiments, the arrays and methods allow for the determination of a pattern of biomarkers associated with the disease state or disease or disorder or, in some embodiments, specific biomarkers that are associated with the disease or disorder. Not only will biomarkers that may be associated with a disease state be able to be identified, for example, biomarkers listed herein, but new biomarkers or patterns of biomarkers that may be associated with a disease state or a disease or disorder may be determined. As discussed above, some biomarkers or patterns of biomarkers for a specific disease or disorder may be a change in a biomolecule associated with the sensor array of the present invention and differ from what is usually referred to as biomarkers in the art, e.g., and increase expression of a specific biomolecule associated with a disease. As discussed above, it may be the interaction of a biomolecule, e.g. biomolecule X, with other biomolecules, e.g. biomolecule Y and Z, that results in the ability to associate with a specific disease state and may not correlate with any change in the absolute concentration of biomarker X in the sample over time or disease state. Thus, a molecule that would not in the conventional sense be considered a biomarker since it does not change in absolute concentration in a sample from the pre-disease to disease state, may in view of the present disclosure be considered a biomolecule as its relative changes that are measured by the array of the present invention are associated with a disease state. In other words, it may be an increase or decrease in the interaction of biomolecule X (due to the interactions of X with the sensor elements and other biomolecules in the sample) with the array that provides a signal that a biomarker is associated with a disease state.

Suitable cancer biomarkers include, but are not limited to, for example, AHSG (α2-HS-Glycoprotein), AKR7A2 (Aflatoxin B1 aldehyde reductase), AKT3 (PKB γ), ASGR1 (ASGPR1), BDNF, BMP1 (BMP-1), BMPER, C9, CA6 (Carbonic anhydrase VI), CAPG (CapG), CDH1 (Cadherin-1), CHRDL1 (Chordin-Like 1), CKB-CKM-(CK-MB), CLIC1 (chloride intracellular channel 1), CMA1 (Chymase), CNTN1 (Contactin-1), COL18A1 (Endostatin), CRP, CTSL2 (Cathepsin V), DDC (dopa decarboxylase), EGFR (ERBB1), FGA-FGB-FGG (D-dimer), FN1 (Fibronectin FN1.4), GHR (Growth hormone receptor), GPI (glucose phosphate isomerase), HMGB1 (HMG-1), HNRNPAB (hnRNP A/B), HP (Haptoglobin, Mixed Type), HSP90AA1 (HSP 90a), HSPA1A (HSP 70), IGFBP2 (IGFBP-2), IGFBP4 (IGFBP-4), IL12B-IL23A (IL-23), ITIH4 (Inter-α-trypsin inhibitor heavy chain H4), KIT (SCF sR), KLK3-SERPINA3 (PSA-ACT), L1CAM (NCAM-L1), LRIG3, MMP12 (MMP-12), MMP7 (MMP-7), NME2 (NDP kinase B), PA2G4 (ErbB3 binding protein Ebp1), PLA2G7 (LpPLA2/PAFAH), PLAUR (suPAR), PRKACA (PRKA C-α), PRKCB (PKC-β-II), PROK1 (EG-VEGF), PRSS2 (Trypsin-2), PTN (Pleiotrophin), SERPINA1 (α1-Antitrypsin), STC1 (Stanniocalcin-1), STX1A (Syntaxin 1A), TACSTD2 (GA733-1 protein), TFF3 (Trefoil factor 3), TGFBI (βIGH3), TPI1 (Triosephosphate isomerase), TPT1 (Fortilin), YWHAG (14-3-3 protein γ), YWHAH (14-3-3 protein eta), prostate cancer biomarkers, for example, PSA, Pro-PSA, PHI, PCA3, TMPRSS3:ERG, PCMT, MTEN, breast cancer markers, for example, epidermal growth factor receptor 2 (HER2) oncogene, melanoma biomarker BRAF, lung cancer biomarker EML4-ALK, A2ML1, BAX, C10orf47, Clorfl62, CSDA, EIFC3, ETFB, GABARAPL2, GUKL GZMH, HIST1H3B, HLA-A, HSP90AA1, NRGN, PRDXS, PTMA, RABACL RABAGAP1L, RPL22, SAP 18, SEPW1, SOX1, EGFR, EGFRvIII, apolipoprotein AI, apolipoprotein CIII, myoglobin, tenascin C, MSH6, claudin-3, claudin-4, caveolin-1, coagulation factor III, CD9, CD36, CD37, CD53, CD63, CD81, CD136, CD147, Hsp70, Hsp90, Rabl3, Desmocollin-1, EMP-2, CK7, CK20, GCDF15, CD82, Rab-5b, Annexin V, MFG-E8, HLA-DR, a miR200 microRNA, MDC, NME-2, KGF, PIGF, Flt-3L, HGF, MCP1, SAT-1, MIP-1-b, GCLM, OPG, TNF RII, VEGF-D, ITAC, MMP-10, GPI, PPP2R4, AKR1B1, Amy1A, MIP-1b, P-Cadherin, EPO and the like. For example, biomarkers for breast cancer include, but are not limited to, ER/PR, HER-2/neu, and the like. Biomarkers for colorectal cancer include, but are not limited to, for example, EGFR, KRAS, UGT1A1, and the like. Biomarkers associated with leukemia/lymphoma include, but are not limited to, e.g., CD20 antigen, CD30, FIP1L1-PDGFRalpha, PDGFR, Philladelphia Chromosome (BCR/ABL), PML/RAR alpha, TPMT, UGT1A1, and the like. Biomarker associated with lung cancer include but are not limited to, e.g., ALK, EGFR, KRAS and the like. Biomarkers are known in the art, and can be found in, for example, Bigbee W, Herberman R B. Tumor markers and immunodiagnosis. In: Bast R C Jr., Kufe D W, Pollock R E, et al., editors. Cancer Medicine. 6th ed. Hamilton, Ontario, Canada: BC Decker Inc., 2003; Andriole G, Crawford E, Grubb R, et al. Mortality results from a randomized prostate-cancer screening trial. New England Journal of Medicine 2009; 360(13):1310-1319; Schroder F H, Hugosson J, Roobol M J, et al. Screening and prostate-cancer mortality in a randomized European study. New England Journal of Medicine 2009; 360(13):1320-1328; Buys S S, Partridge E, Black A, et al. Effect of screening on ovarian cancer mortality: the Prostate, Lung, Colorectal and Ovarian (PLCO) Cancer Screening Randomized Controlled Trial. JAMA 2011; 305(22):2295-2303; Cramer D W, Bast R C Jr, Berg C D, et al. Ovarian cancer biomarker performance in prostate, lung, colorectal, and ovarian cancer screening trial specimens. Cancer Prevention Research 2011; 4(3):365-374; Sparano J A, Gray R J, Makower D F, et al. Prospective validation of a 21-gene expression assay in breast cancer. New England Journal of Medicine 2015; First published online Sep. 28, 2015. doi: 10.1056/NEjMoa1510764, incorporated by reference in their entireties.

Suitable, these methods can be used to determine biomarkers associated with cancer. For example, in one embodiment the cancer is glioblastoma, and wherein the biomarker is selected from the group consisting of HABP1, VTNC, CO3, ITIH2, ITIH1, C07, FHRS, CBPN, ALBU, PLMN, CO4A, PRDX2, VWF, C4BPA, APOB, HBB, CNDP1, CRP, SAA4, APOE, CSCL7 and combinations thereof. In another embodiment, the cancer is meningioma, and wherein the biomarker is selected from the group consisting of FCN3, RET4, HABP2, CBPN and combinations thereof. In another embodiment, the cancer is pancreatic cancer and wherein the biomarker is selected from the group consisting of KNG1, IC1, CBPB2, TRFE, GELS, CXCL7, HPTR, PGK1, AACT, LUM, APOE, FIBB, APOA2, A1BG, A1AT, LBP, APOA1, H4, FIBG and combinations thereof. In another embodiment, the cancer is lung cancer and the biomarker is selected from the group consisting of COO, CRP, SAA4, APOA1, A1AT, GELS and combinations thereof. In another embodiment, the cancer is myeloma and the biomarker is ALBU.

Biomarkers may also be associated with the cardiovascular disease which are known in the art and include, but are not limited to, lipid profile, glucose, and hormone level and physiological biomarkers based on measurement of levels of important biomolecules such as serum ferritin, triglyceride to HDLp (high density lipoproteins) ratio, lipophorin-cholesterol ratio, lipid-lipophorin ratio, LDL cholesterol level, HDLp and apolipoprotein levels, lipophorins and LTPs ratio, sphingolipids, Omega-3 Index, and ST2 level, among others. Suitable biomarkers for cardiovascular disease can be found in the art, for example, but not limited to, in van Holten et al. “Ciculating Biomarkers for Predicting Cardiovascular Disease Risk; a Systemic Review and Comprehensive Overview of Meta-Analyses” PLoS One, 2013 8 (4): e62080, incorporated by reference in its entirety.

Biomarkers may also be associated with a neurological disease. Suitable biomarkers are known in the art and include, but are not limited to, e.g., Aβ1-42, t-tau and p-tau 181, α-synuclein, among others. See, e.g., Chintamaneni and Bhaskar “Biomarkers in Alzheimer's Disease: A Review” ISRN Pharmacol. 2012. 2012: 984786. Published online 2012 Jun. 28, incorporated by reference in its entirety.

Biomarkers for inflammatory diseases are known in the art and include, but are not limited to, e.g., cytokines/chemokines, immune-related effectors, acute-phase proteins [C-reactive protein (CRP) and serum amyloid A (SAA)], reactive oxygen species (ROS) and reactive nitrogen species (RNS), prostaglandins and cyclooxygenase (COX)-related factors, and mediators such as transcription factors and growth factors, which can include, for example, C-reactive protein (CRP), S100, LIF, CXCL1, CXCL2, CXCL4, CXCL5, CXCL8, CXCL9, CXCL10, CCL2, CCL23, IL-Iβ, IL-IRa, TNF, IL-6, IL-10, IL-17A, IL-17F, IL-21, IL-22, IFNγ, CXCRI, CXCR4, CXCR5, GM-CSF, GM-CSFR, G-CSF, G-CSFR, EGF, VEGFA, LEP, SAA1, VCAM1, CRP, MMP1, MMP3, TNFRSF1A, RETN, CHI3L1, antinuclear antibodies (ANA), rheumatoid factor (RF), antibodies against cyclic citrullinated peptide (anti-CCP)] and for chronic IBD (fecal calprotectin), among others. Suitable biomarkers for inflammatory bowel disease, for example, include CRP, ESR, pANCA, ASCA, and fecal calprotectin. See, e.g., Yi Fengming and Wu Jianbing, “Biomarkers of Inflammatory Bowel Disease,” Disease Markers, vol. 2014, Article ID 710915, 11 pages, 2014. doi:10.1155/2014/710915, incorporated by reference in its entirety.

The terms “individual,” “subject,” and “patient” are used interchangeably herein irrespective of whether the subject has or is currently undergoing any form of treatment. As used herein, the term “subject” generally refers to any vertebrate, including, but not limited to a mammal. Examples of mammals including primates, including simians and humans, equines (e.g., horses), canines (e.g., dogs), felines, various domesticated livestock (e.g., ungulates, such as swine, pigs, goats, sheep, and the like), as well as domesticated pets (e.g., cats, hamsters, mice, and guinea pigs). Preferably, the subject is a human.

The arrays and methods described herein can be used under a number of different conditions to provide the desired biomolecule fingerprint. For example, the size of the sensor elements, the rate of flow of the sample through the sensor, the time of incubating the sensor array with the sample and the temperature at which the sensor array is incubated can all be changed to provide a reproducible biomolecule fingerprint. Suitable sizes of the sensor element include nanoscale sensor elements that have less than one micron in at least one direction.

Suitable time for incubating the array or plurality of sensor elements include, at least a few seconds, e.g. at least 10 seconds to about 24 hours, for example at least about 10 seconds, at least about 15 seconds, at least about 20 seconds, at least about 25 seconds, at least about 30 seconds, at least about 40 seconds, at least about 50 seconds, at least about 60 seconds, at least about 90 seconds, at least about 2 minutes, at least about 3 minutes, at least about 4 minutes, at least about 5 minutes, at least about 6 minutes, at least about 7 minutes, at least about 8 minutes, at least about 9 minutes, at least about 10 minutes, at least about 15 minutes, at least about 20 minutes, at least about 25 minutes, at least about 30 minutes, at least about 45 minutes, at least about 50 minutes, at least about 60 minutes, at least about 90 minutes, at least about 2 hours, at least about 3 hours, at least about 4 hours, at least about 5 hours, at least about 6 hours, at least about 7 hours, at least about 8 hours, at least about 9 hours, at least about 10 hours, at least about 12 hours, at least about 14 hours, at least about 15 hours, at least about 16 hours, at least about 17 hours, at least about 18 hours, at least about 19 hours, at least about 20 hours, and include any time and increment in between (e.g. 10 seconds, 11, 12, 13, 14, 15, 15, 17, 18, 19, 20, 21, 22, 23, 24, 25, 26, 27, 28, 29, 30, 31, 32 33, 34, 35, 36, 37, 38, 39, 40, 41, 42, 43, 44, 45, 46, 47, 48, 49, 50, 51, 52, 53, 54, SS, 56, 57, 58, 59, 60 seconds, etc.; 1 minute, 2, 3, 4, 5, 6, 7, 9, 10, 11, 12, 13, 14, 15, 15, 17, 18, 19, 20, 21, 22, 23, 24, 25, 26, 27, 28, 29, 31, 32, 33, 34, 35, 36, 37, 38, 39, 40, 41, 42, 43, 44, 45, 46, 47, 48, 49, 50, 51, 52, 53, 54, 55, 56, 57, 58, 59, 60, etc.; 1 hour, 2 hours, 3, hours, 4, hours, 5 hours, 6 hours, 7 hours, 8 hours etc.)

Further, the temperature at which the assay is performed can be determined by one skilled in the art, and incudes temperatures between about 4° C. to about 40° C., alternatively from about 4° C. to about 20° C., alternatively from about 10° C. to about 15° C., alternatively from about 10° C. to about 40° C., for example, at about 4° C., about 5° C., about 6° C., about 7° C., about 8° C., about 9° C., about 10° C., about 11° C., about 12° C., about 13° C., about 14° C., about 15° C., about 16° C., about 17° C., about 18° C., about 19° C., about 20° C., about 21° C., about 22° C., about 25° C., about 30° C., about 35° C., about 37° C., etc. Suitable, the assay may be performed at room temperature (e.g. around about 37° C., for example from about 35° C. to about 40° C.).

The methods of the present invention may comprise contacting the sample with the sensor array. The contacting of the sample with the sensor array may be using any suitable flow rate in which the sample can flow over the sensor array. In some aspects, the flow velocity of the streams, the Reynolds number, or the relative cross sectional areas of the flow streams can be altered to provide adequate contact between the sample and the sensor array.

For example, in embodiments using a nanochannel or microchannel the cross sectional area of the first stream can be more than 1% of the cross sectional area of the channel. In another example, the cross-sectional area of the first stream can be less than 90% of the cross sectional area of the channel. The cross sectional area ratio can be 10:1 to 1:10, 1:5 to 5:1, 1:3 to 3:1, 1:2 to 2:1 or 1:1.

In certain other circumstances, the flow of the sample over the array has a Reynolds number at the location of the introduction of the sample of between 300 and 1,000,000. In some instances, the location of the introduction of the sample is a nanochannel or microchannel.

Kits

Aspects of the present disclosure that are described with respect to methods can be utilized in the context of the sensor array or kits discussed in this disclosure. Similarly, aspects of the present disclosure that are described with respect to the sensor array and methods can be utilized in the context of the kits, and aspects of the present disclosure that are described with respect to kits can be utilized in the context of the methods and sensor array.

This disclosure provides kits. The kits can be suitable for use in the methods described herein. Suitable kits include a kit for determining a biomolecule fingerprint for a sample comprising a sensor array as described herein. In one aspect, the kit provides a sensor array comprising at least two sensor elements which have differing physiocochemical properties from each other. In some aspects, the kits provides a comparative panel of biomolecule fingerprints in order to use the biomolecule fingerprint to determine a disease state for the subject. In some aspects, instructions on how to determine the biomolecule fingerprint are included. In some suitable embodiments, the sensor arrays are provided as chip arrays in the kit.

In other aspects, kits for determining a disease state of a subject or diagnosing or prognosing a disease in a subject are provided. Suitable kits include a sensor array comprising at least two sensor elements which have differing physiocochemical properties from each other to determining a biomolecule fingerprint. Further, the kit may further include a comparative panel of biomolecule fingerprint of different disease states or different diseases or disorders. Instructions on determining the biomolecule fingerprint and analysis are provided.

It should be apparent to those skilled in the art that many additional modifications beside those already described are possible without departing from the inventive concepts. In interpreting this disclosure, all terms should be interpreted in the broadest possible manner consistent with the context. Variations of the term “comprising” should be interpreted as referring to elements, components, or steps in a non-exclusive manner, so the referenced elements, components, or steps may be combined with other elements, components, or steps that are not expressly referenced. Embodiments referenced as “comprising” certain elements are also contemplated as “consisting essentially of” and “consisting of” those elements. The term “consisting essentially of” and “consisting of” should be interpreted in line with the MPEP and relevant Federal Circuit's interpretation. The transitional phrase “consisting essentially of” limits the scope of a claim to the specified materials or steps “and those that do not materially affect the basic and novel characteristic(s)” of the claimed invention. “Consisting of” is a closed term that excludes any element, step or ingredient not specified in the claim.

The following non-limiting examples are included for purposes of illustration only, and are not intended to limit the scope of the range of techniques and protocols in which the compositions and methods of the present invention may find utility, as will be appreciated by one of skill in the art and can be readily implemented.

EXAMPLES Example 1A. Label-Free Sensor Array for Early Detection of Cancer

The present Example provides a label-free sensor array for early detection of various cancers. The sensor array consists of three different cross-reactive liposomes with various surface charges (i.e., cationic (DOPG (1,2-dioleoyl-sn-glycero-3-phospho-(1′-rac-glycerol)), anionic (DOTAP (1,2-Dioleoyl-3-trimethylammonium-propane)-DOPE (dioleoylphosphatidylethanolamine)), and neutral (CHOL (DOPC-Cholesterol)), whose protein corona composition changes in response to their interactions with the plasma of patients who have different types of various cancers, i.e., lung, pancreas, myeloma, meningioma, and glioblastoma. Although no single protein corona composition is specific for any one cancer type, the changes in the corona composition pattern provide a unique “fingerprint” for each type of cancer.

Hard corona profiles of the sensor array elements using plasma from patients with cancers at early, intermediate, and advanced stages. The composition of the protein corona that forms on the surface of sensor array elements (nanoparticles) is strongly dependent on the physicochemical properties of those nanoparticles and, at the same time, can be strongly affected by the type of disease present in the donor of the human plasma used for incubation. The size and charge of the corona-coated nanoparticles, after incubation with plasma from patients with five different types of cancers (i.e., glioblastoma multiforme, lung cancer, meningioma, multiple myeloma, and pancreatic cancer) and healthy individuals (see Table 1), were probed using dynamic light scattering (DLS/Nanosight) and transmission electron microscopy (TEM), and the results demonstrated that the physicochemical properties of the corona-coated nanoparticles depended substantially on the type of cancer (FIGS. 2A,B).

TABLE 1 General information on patients (and their cancer types) whose plasma was used in this study. CANCER STAGE PATIENT LABEL AGE GENDER CANCER STAGE CATEGORY HEALTHY 1 43 F — — HEALTHY 2 54 M — — HEALTHY 3 67 F — — HEALTHY 4 69 M — — HEALTHY 5 61 F — — PANCREAS 1 81 M TNM: cT4 N+ M+ Advanced PANCREAS 2 76 M TNM: cT2 N+ Moderate PANCREAS 3 60 F TNM: cT4 N+ Advanced PANCREAS 4 75 M TNM: cT3 N+ M+ Advanced PANCREAS 5 61 F TNM: cT3 N+ M+ Advanced PANCREAS 6 71 F TNM: cT3 N+ Advanced PANCREAS 7 61 M TNM: cT3 N+ Advanced PANCREAS 8 67 M TNM: cT3 N+ Advanced LUNG 1 45 F TNM: TIA N0 M0 Early LUNG 2 24 M TNM: TIA N0 M0 Early LUNG 3 44 F TNM: TIA N0 M0 Early LUNG 4 48 F TNM: TIA N0 M0 Early LUNG 5 40 M TNM: TIA N0 M0 Early LUNG 6 47 F TNM: TIA N0 M0 Early LUNG 7 51 M TNM: TIA N0 M0 Early LUNG 8 52 F TNM: TIA N0 M0 Early MYELOMA 1 41 F Onset II (52% Plasma cells in Bone Moderate Marrow; Monoclonal IgG-k) MYELOMA 2 60 F Onset I (28% Plasma cells in Bone Early Marrow; Monoclonal IgG-k) MYELOMA 3 57 F Onset I (8% Plasma cells in Bone Early Marrow; Monoclonal IgG-k) MYELOMA 4 63 M Onset I (9% Plasma cells in Bone Early Marrow; Monoclonal IgG-k) MYELOMA 5 75 M Onset II (42% Plasma cells in Bone Moderate Marrow; Monoclonal IgG-k) MYELOMA 6 46 F Onset I (15% Plasma cells in Bone Early Marrow; Monoclonal IgG-L) MYELOMA 7 56 F Onset I (44% Plasma cells in Bone Early Marrow; Monoclonal IgG-L) MYELOMA 8 70 F Onset I (27% Plasma cells in Bone Early Marrow; Monoclonal IgG-L) GLIOBLASTOMA 1 58 M WHO 4 Advanced GLIOBLASTOMA 2 75 M WHO 4 Advanced GLIOBLASTOMA 3 76 M WHO 4 Advanced GLIOBLASTOMA 4 73 M WHO 4 Advanced GLIOBLASTOMA 5 76 F WHO 4 Advanced GLIOBLASTOMA 6 62 M WHO 4 Advanced GLIOBLASTOMA 7 48 M WHO 4 Advanced GLIOBLASTOMA 8 56 M WHO 4 Advanced MENINGIOMA 1 82 F WHO 2 Moderate MENINGIOMA 2 50 F WHO 2 Moderate MENINGIOMA 3 80 M WHO 2 Moderate MENINGIOMA 4 67 M WHO 2 Moderate MENINGIOMA 5 64 M WHO 2 Moderate MENINGIOMA 6 84 M WHO 2 Early MENINGIOMA 7 58 F WHO 2 Early MENINGIOMA 8 70 M WHO 2 Early

Quantitative evaluation of the total protein adsorbed onto the nanoparticles was performed via the BCA or NanoOrange assay, and the results showed significant differences in the amounts of adsorbed proteins after incubation in plasma from patients with various types of cancers (FIG. 2B). The quantitative evaluation of the total protein adsorbed on the surface of liposomes showed strong dependency of protein amount on cancer type (FIG. 2B). The protein corona composition at the surface of three liposomes was evaluated by liquid chromatography-mass spectrometry (LC-MS/MS) in which the abundance of 1,800 known proteins was defined. The contribution of individual proteins and their categories (i.e., complement, coagulation, tissue leakage, lipoproteins, acute phase, immunoglobulins, and other plasma proteins) to the corona composition were defined (FIG. 2C; FIGS. 3A-F). These results demonstrated significant associations between the protein composition and not only the cancer type but also the type of sensor element (i.e., type of nanoparticle).

According to an extensive body of literature, there are considerable relationships between cancer development and variations in complement, coagulation, tissue leakage, lipoproteins, acute phase, and immunoglobulins. Therefore, the cross-reactive interactions of these protein categories with nanoparticles may provide unique “fingerprints” for each type of cancer, which may facilitate cancer identification and discrimination. Consequently, one would expect the protein corona sensor array to cross-reactively adsorb a wide range of proteins involved in cancer induction and development that could be used for cancer identification and discrimination.

Develop supervised classification analysis to identify and discriminate among cancers using the protein corona sensor array outcomes. In order to investigate whether protein corona fingerprints (PCFs) of various sensor elements could be utilized as a biosensors and form unique patterns for different diseases, we have applied focused classification approaches to proteomic data on three liposomes' protein corona composition (cationic, anionic, and neutral). Details of the methods are described in the Methods section. A weighted-variable importance in the projection (VIP) score is introduced and applied for ranking of variables based on partial least squares discriminant analysis (PLS-DA) as a linear projection method. Selection of the most relevant variables (proteins) in building the classification model can be guided by a set of obtained ranked variables. In this regard, top ranked variables were added to the model one by one, and the classification error of the PLS-DA model was monitored. We observed that the classification model has the minimum error by using only the top 69 features (FIG. 4A). The new 69-dimensional feature space was successfully used to discriminate samples belonging to six classes by PLS-DA with a high classification accuracy (0.97) using leave-one-out and 10-fold cross-validation (FIGS. 4A,B). The classification parameters are given in Table 2. The contribution of each single selected protein to the separation of each cancer group (VIP) is plotted on the y- and x-axis, respectively, to provide a visual representation of the relative specificity of the findings (FIGS. 4B-F). The proteins with higher VIP scores could be considered the best informative or diagnostic set to discriminate each disease from controls and from among all cancer categories.

TABLE 2 Classification results obtained from two developed and non-linear models for six groups of samples. PLS-DA, 10 fold CV, Models/classification LV = 5 CPANN (8*8 ) parameters 20 iteration 10 fold CV Specificity (CV) 1 1.00 1.00 2 0.96 0.96 3 1.00 1.00 4 1.00 1.00 5 1.00 1.00 6 1.00 1.00 Sensitivity (CV) 1 1.00 1.00 2 1.00 1.00 3 1.00 0.80 4 1.00 1.00 5 1.00 1.00 6 1.00 1.00 Class error (CV) 1 0.00 0.00 2 0.03 0.02 3 0.00 0.00 4 0.00 0.00 5 0.00 0.00 6 0.00 0.00 1) Control 2) Glioblastoma 3) Meningioma 4) Myeloma 5) Pancreas 6) Lung cancers

PLS-DA and counter propagation artificial neural network (CPANN) were then applied to the selected variables, and whole samples as supervised classification, linear, and non-linear approaches, respectively. It should be noted that the primary data set with all variables before variable selection, has poor discrimination and could not be separated into six groups.

Next, to further verify and analyze the data, we decided to take advantage of a non-linear classification method. Visualizing the feature space can help us understand the hidden structures and topological relationships among the patterns. To reduce the dimensionality of the feature space while preserving the topological relation in the data structure, the CPANN (a supervised variant of self-organizing maps/SOM) was used to learn and predict the class membership of the patterns, simultaneously producing a two-dimensional map of neurons and provide valuable information (from a non-linear approach) about the data structure. Details of the CPANN are provided in the Methods section. Different sizes for the CPANN map were checked using 10-fold cross-validation; a map including 64 (8×8) neurons was chosen due to the minimum classification error (FIG. 9C). Moreover, the topological structure of data in the high-dimensional space is reflected in the assignation map produced by CPANN (FIGS. 5C,D). Considering the similarity of the neurons to the input vectors, the map can be partitioned into six distinct zones related to different type of cancers and control samples. Samples with the same class label are mapped onto nearby or the same neurons, which means that the selected variables provide information valuable in discriminating the samples in the feature space. The relative position and orientation of six zones on the map can contribute qualitative information on the similarities between types of cancers. To represent the effect of variable selection on the quality of mapping, another CPANN was trained with all 1823 variables, and the resulting map shows that the selected biomarkers (variables) play an important role in discriminating among cancer types and classifying them properly (FIGS. 5C,D).

On the basis of the obtained results, both linear and non-linear models showed high accuracy, deduced from their acceptable specificity, sensitivity, and class error values. Consistent with these findings, unsupervised clustering (HCA) based on 69 markers was able to strongly separate, various type of cancerous and control samples (FIG. 5E-F). As can be seen in FIG. 5 , there is close similarity between the glioblastoma and meningioma groups of samples, implying difficulty in discrimination, most probably related to similar plasma proteomics patterns in these two brain cancers. These results reflect the fact that the plasma concentrations of many proteins in the corona differ considerably, not only among subjects with different types of cancers, but among healthy individuals as well.

To illustrate the biosensors' capability for pattern recognition, a set of analyses was performed on the data obtained from individual nanoparticles. As expected, the pattern of cancer-specific fingerprints could not be extracted solely from each nanoparticle's PCF. We found that pattern-recognition techniques applied to protein abundance in the protein corona formed on three different liposomes (cationic, anionic, and neutral) correctly distinguished not only cancerous from control samples, but also each type of cancer under consideration from the others.

Identification of proteins with crucial roles in cancer detection and discrimination as promising biomarkers for specific types of cancers. The use of biomarkers both before cancer diagnosis (in risk assessment and screening/early detection) and after diagnosis (in monitoring therapy, selecting additional therapy, and detecting recurrence) would yield substantial therapeutic and health-economic benefits. To understand the potential biological relevance of the 69 selected proteins that discriminate cancerous samples, we manually searched through previously published reports in PubMed on protein biomarkers of specific types of cancers that are upregulated or downregulated according to different disease stages. The resulting data were compared with the selected proteins in the model to identify matched markers and determine the biological relevance of the proposed model. Interestingly, we noted significant numbers of biomarkers specific to five investigated groups of cancers among the selected predictors that had been reported as specific cancer biomarkers (FIG. 7B).

The high specificity of the selected markers for discriminating among the five groups of cancers, which derives from the introduced protein corona sensor array approach, demonstrates a significant correlation with the work now under way in the complex cancer proteomics space; therefore this strategy not only provides a basis for cancer prediction but also translates that promise into reality. It is noteworthy that the discrimination between different groups occurs as a result of several predictors (and not individual biomarkers) that change simultaneously in a systematic manner, forming patterns unique to each specific type of cancer. On the basis of this evidence, the most informative predictors selected by the proposed model that have not already been reported as cancer-specific biomarkers may have great potential as new diagnosis biomarker candidates. To define their role in cancer development, the variation and functionality of these promising candidates in cancer patients should be carefully monitored. By focusing on the unique patterns derived from huge numbers of subjects via a set of informative predictors, researchers should be able to predict cancers at different stages more accurately than is possible using current methods.

Cohort data analysis. To probe the capacity of this innovative sensor array for very early detection of cancers, we used cohort plasma from healthy people who were diagnosed with one of the five types of cancers several years after plasma collection. Using the cohort samples, we evaluated whether our proposed models, both linear and non-linear, with 69 selected predictors could be utilized for cancer prediction.

To this end, the values related to 69 variables were put into the model, and the class membership of each cohort object was predicted given the fixed optimum parameters values. It is noteworthy that 19 variables (proteins), out of the 69 variables, were absence in the proteomics profile of protein corona sensor array of cohort samples; therefore their amount in the validation data matrix was zero. Interestingly, both linear and non-linear models provided good predictions for all five samples. The observed distance between training and cohort samples (FIGS. 6A,B), most probably influenced by zero values that were added to data matrix for those 19 absent variables. As shown in FIGS. 6C, D, the cohort samples were placed in the correct neuron related to Glioblastoma in the CPANN map. METHODS

Liposomes. Cholesterol (Chol) was purchased from Sigma Aldrich (St. Louis, MO, USA). DOPC (dioleoylphosphatidylcholine), DOPE (dioleoylphosphatidylethanolamine), DOPG (1,2-dioleoyl-sn-glycero-3-phospho-(1′-rac-glycerol)), and DOTAP (1,2-Dioleoyl-3-trimethylammonium-propane) were purchased from Avanti Polar Lipids (Alabaster, AL, USA). DOPG, DOTAP-DOPE (1:1 molar ratio) and DOPC-Chol (1:1 molar ratio) liposomes were prepared by dissolving appropriate amounts of lipids 9:1 (v/v) in chloroform:methanol. The chloroform:methanol mixture was evaporated by rotary-evaporation. Lipid films were kept under vacuum overnight and hydrated with phosphate saline buffer (PBS) 10 mmol/l (pH 7.4) to a final lipid concentration of 1 mg/ml. The liposome suspensions obtained were sized by extrusion through a 50-nm polycarbonate carbonate filter by the Avanti Mini-Extruder (Avanti Polar Lipids, Alabaster, AL).

Human plasma collection, preparation, and storage. Human plasma (HP) was collected from healthy and cancer patients diagnosed with glioblastoma multiforme, lung cancer, meningioma, multiple myeloma, or pancreatic cancer. The present study was approved by the Ethical Committees of the Sapienza University of Rome (glioblastoma multiforme, meningioma, multiple myeloma), the University of Napoli Federico II (lung cancer), and the University Campus Bio-Medico di Roma (pancreatic cancer). In brief, blood was collected by venipuncture of healthy subjects and cancer patients by means of a BD P100 Blood Collection System (Franklin Lakes, NJ, USA) with push-button technology that reduces blood waste while minimizing the risk of contamination. After clot formation, samples were centrifuged at 1000×g for 5 min to pellet the blood cells, and the supernatant was removed. After confirming the absence of hemolysis, plasma collected from each donor (1 ml) was split into 200-microliter aliquots and stored at −80° C. in labeled Protein LoBind tubes until use. For analysis, the aliquots were thawed at 4° C. and then allowed to warm at room temperature (RT).

Cohort plasma samples. We used human plasma from healthy people diagnosed with brain, lung, and pancreatic cancers within eight years after plasma collection. The plasma samples were collected through the NIH-funded Golestan Cohort Study, performed by the National Cancer Institute (NCI) in the USA, the International Agency for Research on Cancer (IARC) in France, and the Tehran University of Medical Sciences (TUMS) in Iran. This study involved the collection and storage of plasma from 50,000 healthy subjects, over 1,000 of whom went on to develop various types of cancers in subsequent years. Samples from five individuals per cancer were used in this study. These important plasma samples provide us the unique opportunity to probe the capacity of our innovative protein corona sensor array for early detection of cancers.

Size and zeta-potential. Bare liposomes were incubated with HP (1:1 v/v) for 1 hour at 37° C. Subsequently samples were centrifuged at 14000 rpm for 15 minutes at 4° C. to pellet liposome-HP complexes. The resulting pellet was washed three times with phosphate-buffered saline (PBS) and resuspended in ultrapure water. For size and zeta-potential measurements, 10 μL of each sample were diluted with 990 μL of distillated water. All size and zeta-potential measurements were performed at RT using a Zetasizer Nano ZS90 (Malvern, U.K.) equipped with a 5-mW HeNe laser (wavelength λ=632.8 nm) and a digital logarithmic correlator. The normalized intensity autocorrelation functions were analyzed by the CONTIN method to obtain the distribution of the diffusion coefficient D of the particles. D is converted into an effective hydro-dynamic radius R_(H) by the Stokes-Einstein equation (R_(H)=K_(B)T/6πηD), where K_(B)T is the thermal energy and η is the solvent viscosity. Electrophoretic mobility of samples, u, was measured by laser Doppler electrophoresis. Zeta-potential was calculated by the Smoluchowski relation (zeta potential=uη/ε) where η and ε are the viscosity and the permittivity of the solvent phase, respectively). Size and zeta-potential of liposome-HP complexes are given as mean±standard deviation (S.D.) of five independent measurements.

Protein assay. Liposome formulations were incubated with HP (1:1 v/v) for 1 hour at 37° C. Afterwards, liposome-HP complexes were pelleted at 15000×g for 15 minutes at 4° C. and washed three times with PBS. Washed pellet was resuspended in urea 8 mol/l, NH₄CO₃ 50 mmol/l. 10 microliters of each sample were added to five wells of a 96-well plate. Protein quantification was made adding 150 microliters/well of Protein Assay reagent (Pierce, Thermo Scientific, Waltham, MA, USA). The multiwell was shaken and incubated at room temperature for 5 minutes. Absorbance was measured with GloMax Discover System (Promega, Madison, WI, USA) at 660 nm. Background effects were properly corrected and the protein concentration was calculated using the standard curve. Results are given as mean±S.D. of five independent replicates.

Protein identification and quantification. The incubation procedure was performed as described elsewhere (Label-free quantitative analysis for studying the interactions between nanoparticles and plasma proteins. Analytical and Bioanalytical Chemistry, 2013, 405, 2-3, 635-645, incorporated by reference in its entirety). Liposome formulations were incubated with HP (1:1 v/v) for 1 hour at 37° C. Samples were centrifuged at 15000×g for 15 min to pellet liposome-HP complexes. The pellet was washed three times with 10 mmol/l Tris HCl (pH 7.4), 150 mmol/l NaCl and 1 mmol/l EDTA. After washing, the pellet was air dried and resuspended in the digestion buffer. The digestion and peptide desalting were carried out as previously described (Shotgun proteomic analytical approach for studying proteins adsorbed onto liposome surface. Analytical and Bioanalytical Chemistry, 2013, 401, 4, 1195-1202, incorporated by reference in its entirety). In brief, pellet was resuspended in 40 microliters of urea 8 mol/l, NH₄CO₃ 50 mmol/l and digested by adding 2 micrograms of trypsin. The digested peptides were desalted using SPE C18 column, reconstituted with a suitable volume of a formic acid solution, and stored at −80° C. until analysis. Digested peptides were analyzed by nano-high-performance liquid chromatography (HPLC) coupled to tandem mass spectrometry (MS/MS). NanoHPLC MS/MS analysis was carried out using a Dionex Ultimate 3000 (Dionex Corporation Sunnyvale, CA, U.S.A.) directly connected to a hybrid linear ion trap-Orbitrap mass spectrometer (Orbitrap LTQ-XL, Thermo Scientific, Bremen, Germany) by a nanoelectrospray ion source. Peptide mixtures were enriched on a 300 μm ID×5 mm Acclaim PepMap 100 C18 precolumn (Dionex Corporation Sunnyvale, CA, U.S.A.), employing a premixed mobile phase made up of ddH2O/ACN, 98/2 (v/v) containing 0.1% (v/v) HCOOH, at a flow-rate of 10 microliters/min. Peptide mixtures were then separated by reversed-phase (RP) chromatography. The largest set of peptides was detected using a 3-hour optimized LC gradient composed of a mobile phase A of ddH2O/HCOOH (99.9/0.1, v/v) and a mobile phase B of ACN/HCOOH (99.9/:0.1, v/v). MS spectra of eluting peptides were collected over an m/z range of 350-1700 using a resolution setting of 60,000 (full width at half-maximum at m/z 400), operating in the data-dependent mode. MS/MS spectra were collected for the five most abundant ions in each MS scan. Further details can be found elsewhere (Shotgun proteomic analytical approach for studying proteins adsorbed onto liposome surface. Analytical and Bioanalytical Chemistry, 2013, 401, 4, 1195-1202). For each experimental condition three independent samples (biological replicates) were prepared, each of which was measured in triplicate (technical replicates), yielding nine measurements for each experimental condition. RAW data files were submitted to Mascot (v2.3, Matrix Science, London, UK) using Thermo-Finningan LC Q/DECA RAW file data import filter to perform database searches against the non-redundant Swiss-Prot database (09-2014, 546000 sequences, Homo Sapiens taxonomy restriction). For the database search, trypsin was specified as the proteolytic enzyme with a maximum of two missed cleavages. Carbamidomethylation was set as fixed modification of cysteine, whereas oxidation of methionine was chosen as variable modification. The monoisotopic mass tolerance for precursor ions and fragmentation ions were set to 10 ppm and 0.8 Da, respectively. Charge state of +2 or +3 were selected as precursor ions. Proteome output files were submitted to the commercial software Scaffold (v3.6, Proteome Software, Portland, Oregon, USA). Peptide identifications were validated if they surpassed a 95% probability threshold set by the PeptideproPhet algorithm. Protein identifications were accepted if they could be established at greater than 99.0% probability and contained at least two unique peptides. Proteins that contained shared peptides and could not be differentiated on the basis of MS/MS analysis alone were grouped to satisfy the principles of parsimony. Unweighted spectrum counts (USC) were used to assess the consistency of biological replicates in quantitative analysis, and normalized spectrum counts (NC S) was used to retrieve protein abundance.

Statistical Analysis. All statistical analyses were performed using PLS, Kohonen, and CPANN toolboxes, and graphs were created using Microsoft Excel, XLSTAT, and MATLAB.

Data matrix. Each raw of the predictor matrix (X) relating to each individual is derived from all proteins' abundance obtained from the three-protein corona sensor array (FIG. 4A). In the preprocessing step, the normalized data in matrix X, relative protein abundance (RPA), were auto-scaled.

Classification and Clustering.

Partial least squares discriminant analysis (PLS-DA). Partial least squares discriminant analysis is a well-known multivariate approach regarded as a linear classification and dimension reduction method consisting of two main parts a structural part, which searches for latent variables as linear combinations of original independent variables (i.e., data matrix X), which have the maximum covariation with the corresponding dependent-variables (i.e., class membership, Y). The measured components include the latent variables as scores and loadings, which show how the latent variables and their original ones are related. Based on the ability of PLSDA to reduce the dimensionality of the data, it allows a linear mapping and graphical visualization of the different data patterns. PLS-DA is particularly well suited to deal with highly collinear and noisy patterns. The main problems associated with the large dataset in proteomics are the large number of monitored variables (i.e., proteins) and relatively small number of samples. Hence, there may be a high redundancy among variables, which render many of them uninformative and irrelevant to the classification. In this way, eliminating uninformative variables or finding new uncorrelated ones may improve the predictive performance of classification. Since in biomedical applications such as the present work, we must not only make decisions about whether a sample belongs to one of a number of known groups, but also determine which variables are most relevant for the best discrimination between classes, a method like PLS-DA is a good candidate approach for finding uncorrelated new latent variables while preserving the variation of the data The impotence power of the original variables to produce latent projections can also be calculated by the variable importance in the projection (VIP) analysis and can play a significant role in to decide about variables.

Identifying the most relevant variables based on weighted VIP. The partial least squares discriminant analysis (PLS-DA) was used to explore the VIP values associated with variables. VIP is a combined measure of how much a variable contributes to a description of the two sets of data: the dependent (Y) and the independent variables (X). The weights in a PLS model reflect the covariance between the independent and dependent variables, and the inclusion of the weights allows VIP to reflect not only how well the dependent variable is described but also how important that information is for the model of the independent variables.

An approach based on VIP score was developed to identify the best subset of variables. VIP scores can be calculated by performing PLS-DA on the dataset. In that approach, VIP scores of variables are calculated 50 times, each time using a random permutation of training and validation sets (random training sets were selected iteratively by considering 80-percent coverage of each class of objects). Considering the most important variables, the large VIP-score values (>2), the top 200 variables can be selected at each repetition and added to the top-variables pool. Afterward, a frequency of occurrence (Freq_(i)) and an average VIP-score (VIP _(i)) for each variable can be obtained according to the top-variables pool. Thus, the selection of variable i (which has a high VIP _(i) value and low VIP _(i) value) is less recommended because of dependency on the training and validation sets. Therefore, the VIP value of each variable can be weighted by Freq_(i), and ranking of the most relevant variables can be done using the weighted VIP _(i). Fig_appr is a schematic diagram of the proposed approach. Selection of the most relevant variables to build the classification model can be guided by the obtained ranking as follows: The highly ranked variables were added one by one to the dataset, and the classification error of PLS-DA was calculated to find the minimum number of relevant predictors (FIG. 4A).

Counter-Propagation Artificial Neural Network (CPANN). The counter-propagation artificial neural network (CPANN) is a supervised variant of self-organizing map that consists of two layers of neurons arranged on a predefined N×N grid. CPANN can be used to map data from a high-dimensional feature space to a low-dimensional (typically 2) discrete space of neurons as well as to predict the class membership of the unknown samples. The input vectors (sample feature vector) and corresponding class membership vectors (a binary vector) are presented to the input and output layer of CPANN, respectively. The weight correction of the neurons in both layers performs based on competitive learning and cooperation of the neurons (See FIG. 67 , Table 3). Hence, similar input vectors can be mapped on the same or adjacent neurons and vice versa. The final assignation map properly reveals the structure of the data in feature space and preserves the distance of patterns in the low-dimensional grid of neurons. FIG. 9C shows a high-quality assignation map of CPANN using top-ranked biomarkers. According to the distinct regions for each class, the risk of classification error is minimized. The proper size of the map can be decided by performing 10-fold cross-validation at different map sizes. The trained CPANN can be used to assign a class membership to an unlabeled sample. Presence of redundant and uninformative variables in training data will affect the quality of the map and increase the risk of an error of classification (FIG. 5C). The process is a nonlinear mapping, which helps visualize a high-dimensional input object on a two-dimensional neuron grid. It is a self-organized procedure and solves the issue of classification in a transparent way. More details about the CPANN method can be found in the following references.

Hierarchical clustering analysis (HCA). Hierarchical clustering analysis is an unsupervised method widely used to explore and visualize whole heterogeneous large data sets like those often used in proteomics into distinct and homogeneous clusters. Strategies for hierarchical clustering can be divided into two categories: agglomerative and divisive methods. The agglomerative procedure first separates each object into its own individual cluster and then combines the clusters sequentially; similar objects or clusters are merged until every object belongs to only one cluster. The divisive procedure, in contrast, starts with all of the objects in one large cluster and gradually partitions them into smaller clusters until each object is in an individual cluster. Finally, objects are organized into a dendrogram whose branches are the defined clusters. In cluster analysis, to identify homogeneous sub-groups, the two important concepts, similarity (determining a numerical value for the similarity between objects and constructing a similarity matrix) and linkage (connection of an object to a group or not) should be defined. Herein, we applied agglomerative hierarchical clustering with furthest-neighbor linkage algorithm for unsupervised analysis based on the selected variables.

Cohort sample prediction. The predictive ability of both linear and non-linear variables, with 69 selected predictors, were assessed by cohort samples analysis. To this end, the values related to 69 variables were put into the model, and the class membership of each cohort object was predicted at the fixed optimum parameters values. The 19 variables (proteins) in the proteomics profile of our protein corona sensor array of cohort samples were not detected, and zero were considered for these variables in validation data matrix. Interestingly, both linear and non-linear models provide good predictions for all five samples. The distance between training and cohort samples shown in FIG. 6A is most probably related to zero values that were added to the data matrix for those 19 absent variables. We examined the effect of replaced zero values for absent variables by deleting these 19 proteins from both data matrices of the training and prediction sets; then the PLS-DA model was built and cohort samples were predicted. As expected, no large distance between cohort and training samples was observed.

Table 3. See FIG. 67 Correlation coefficient of CPANN weight map for each variable in the six classes. For each variable, the correlation coefficient of corresponding weight map with the assignation map pattern can be calculated. CC=0: indicates no correlation between biomarker and the related class; 1>CC(i)>0: accordance between the biomarker intensity and cancer related class. 0<CC<-1: an inverse correlation between biomarker value and cancer-related class. The CC values >0.5 or <−0.5 are colored. For example, the weight map of biomarker 1282 is highly correlated with the cancer class 4 pattern on the assignation map, and it may be an important biomarker for the samples from patients with myeloma.

Example 1B. In Depth Analysis of Human Proteome Using Multi-Nanoparticle Protein Corona Characterization and Machine Learning Enable Accurate Identification and Discrimination of Cancers at Early Stages

In a second embodiment, the collective protein corona data for a given plasma sample, derived from individual nanoparticles' protein corona profiles, is able to identify and discriminate different types of cancers using machine learning (e.g., random forest approach) to analyze the data. The sensor array as described in Example 1A was used and the data collected was further analyzed by machine learning in further detail. This sensor array (i.e. protein corona nanosystem) unambiguously and robustly identified cancer and allows for the discrimination among different types of cancers. This system can be used to predict cancer types using blind plasma samples. The capacity for very early detection by using the plasma of healthy people in existing cohorts who were diagnosed with cancers several years after plasma collection to determine a pre-cancer biomolecule fingerprint.

FIG. 1 presents a schematic overview of the use of the sensor array (nanoparticle system) to use multi-protein-corona proteomics for cancer detection in known cancer patients and for cancer prediction using both blind plasma and cohort samples.

Results

Protein Corona Profiles of the Nanosystem Using Plasma from Patients with Cancers at Early, Intermediate, and Advanced Stages

Our protein corona nanosystem consists of three different cross-reactive liposomes with various surface charges [amionic (DOPG (1,2-dioleoyl-sn-glycero-3-phospho-(1′-rac-glycerol))), cationic (DOTAP (1,2-Dioleoyl-3-trimethylammonium-propane)-DOPE (dioleoylphosphatidylethanolamine)), and neutral (CHOL (DOPC-Cholesterol))], whose protein corona profiles were measured after exposure to the plasma of healthy subjects or patients with one of five cancers: lung, pancreas, myeloma, meningioma, or glioblastoma.

We performed proteomic analysis on each patient (5 patients/group) in triplicate for each of the three liposomes (see FIG. 2A,B for details on the size and charge of the liposomes) in our protein corona nanosystem (i.e., total trials: 3*(29)*3=261). Although no single protein corona composition is specific for any one cancer type as also described in Example 1A, the collective protein corona composition for a given plasma sample derived from different liposomes provided a unique “fingerprint” for each type of cancer.

Though the composition of the protein corona that forms on the surface of liposomes is strongly dependent on their physicochemical properties, it can also be strongly affected by the unique type, concentration, and conformation of proteins and other biomolecules present in a given patient's plasma. The size and charge of corona-coated liposomes were probed using dynamic light scattering (DLS/Nanosight), after incubation with plasma from patients with five different types of cancers (see Table 1) and healthy individuals. The results confirmed that the physicochemical properties of the corona-coated nanoparticles varied across different types of cancer (FIGS. 2A,B).

Quantitative evaluation of the total protein adsorbed onto the liposomes was performed via the BCA (bicinchoninic acid) or NanoOrange assays, and the results confirmed significant differences in the amounts of adsorbed proteins after incubation in plasma from patients with various types of cancers (FIGS. 3A-F). Quantitative evaluation of the total protein adsorbed onto the surface of liposomes showed the dependency of protein amount on cancer type (FIGS. 3A-F). The protein corona composition at the surface of three liposomes was evaluated by liquid chromatography-tandem mass spectrometry (LC-MS/MS) in which 876 known proteins were defined. The contributions of individual proteins and their categories (i.e., complement, coagulation, tissue leakage, lipoproteins, acute phase, immunoglobulins, and other plasma proteins) to the corona composition were defined (FIGS. 3A-F). The results demonstrated associations between the protein composition and not only the cancer type but also the type of liposomes. The mechanism behind this variation is that the high surface-to-volume ratio of the nanoparticles provides a unique opportunity for a wide range of human plasma proteins (highly abundant proteins, less-abundant plasma proteins, and very rare proteins) to participate in the corona composition, without need for depletion of highly abundant proteins, and without a direct correlation to plasma protein concentrations. Furthermore, in our system, conformational changes in plasma proteins can also change the protein corona composition, via significantly altering the interaction site of proteins with nanoparticles. These characteristics make the protein corona profile unique among other approaches developed for the analysis of proteins in human plasma.

The protein corona compositions at the surface of liposomes contained a wide range of human plasma proteins including highly abundant proteins (e.g., albumin, transferrin, complement proteins, apolipoproteins, and alpha-2-macroglobulin) and very rare proteins (defined as <100 ng/ml) such as transforming growth factor beta-1-induced transcript 1 protein (˜10 ng/ml), fructose-bisphosphate aldolase A (˜20 ng/ml), thioredoxin (˜18 ng/ml), and L-selectin (˜92 ng/ml). We also identified 388 proteins without a known previous plasma concentrations (see website at plasmaproteomedatabase.org[[/]]). The obtained protein information was then analyzed by a machine learning approach to probe the capacity of our protein corona nanosystem for robust and accurate cancer detection.

Development of Classifier to Detect and Discriminate Among Cancers Using Protein Corona Nanosystem Outcomes.

To evaluate the ability of the protein corona nanosystem to detect various cancers, we used proteomic data collected from the 3 distinct liposomes on 29 plasma samples (5 patients each from 5 cancer types; and 4 healthy samples) to train a classifier, specifically an algorithm that receives array measurements from a patient and outputs one of six labels (either one of the five cancer types, or healthy). Before training the classifier, raw data from the 3 nanoparticles were first ‘de-noised’ via a low-rank tensor factorization discussed in depth in a later section. This de-noising implicitly mitigates the significant variability observed in individual corona elements. We then trained a random forest classifier, a popular non-linear classification algorithm, on the resulting de-noised data.

We tested the accuracy of this classifier on 16 blind samples (3 patients each from 5 cancer types; and 1 healthy sample). We measured overall classification accuracy for the task of correctly assigning these blind samples to one of the six labels, along with sensitivity and specificity for each of the five cancer types separately (Table 4). Due to the relatively small number of plasma samples (45 in total), and to ensure the robustness of our results, we performed this procedure (training a random forest classifier on 29 samples and measuring accuracy, sensitivities and specificities on the remaining 16 samples) a total of 1000 times. The training and tests sets in each of the 1000 replications of the experiment were chosen randomly from amongst all class-stratified partitions of the data. This approach allows us to calculate unbiased estimates of the p-value for the classification accuracies we report (see Table 4). Specifically, the last row of Table 4 shows that the average overall accuracy across the 1000 replications was 96.2%, or equivalently an overall error of 3.8%. We also observe a p-value of 0.04 for the null hypothesis that the overall classification error is lower than 87.5%, and therefore we can reject this null hypothesis with 95% confidence. Sensitivities for the five individual cancer types range from 87.4% to 100.0%, and individual specificities range from 97.0% to 100.0%.

TABLE 4 Overall classification accuracy, sensitivity, and specificity. Overall classification accuracy for protein corona nanosystem with one, two, and three liposomes (Column 2). Both classification accuracy and the associated p-values improve with additional liposomes. Individual sensitivity and specificity for glioblastoma, lung, meningioma, myeloma, and pancreatic cancers (Columns 3-12) also show that sensitivity and specificity improve with additional liposomes. Experimental results are averaged over 1000 independent draws of a training set comprising 29 plasmas, with evaluation on the remaining 16 plasmas. p-values are for the null hypothesis of a classification error lower than 87.5%. Array Glioblastoma Lung Meningioma Myeloma Pancreatic Size Accuracy Sens. Spec. Sens. Spec. Sens. Spec. Sens. Spec. Sens. Spec. One 86.0 (0.43) 80.1 96.5 85.9 98.4 83.9 96.3 88.1 97.1 89.6 97.7 Two 92.4 (0.18) 89.6 97.5 94.0 99.5 91.6 96.2 99.9 99.6 85.8 99.9 Three 96.2 (0.04) 100.0 98.9 94.0 100.0 98.5 97.0 100.0 100.0 87.4 99.5

The Value of Multi-Liposomes in the Protein Corona Nanosystem

To assess the importance of including multi-liposomes in the protein corona nanosystem, we repeated the entire classification procedure using 1000 different splits of the data into training and testing samples, but this time using data measured from only a single liposome. This was done for each of the three liposomes, and the results are reported in the first row of Table 4. Relative to the entire array including all three liposomes, the single-liposome arrays showed significantly lower accuracy, sensitivity, and specificity. We also re-performed the procedure for sets of two liposomes (there are three such unique sets); these results are found in the second row of Table 4. The two-liposome systems are more accurate than a one-liposome system, but still weaker than the entire array of three liposomes. Overall, this indicates the value of changes in the corona composition pattern between different liposomes and the necessity of including such multiple observations.

Variable and Protein Importance and Stability

The random forest model also yields an importance score for each variable (i.e. each liposome-protein pair). This score essentially measures how important that variable was in discriminating patients of different cancer types. On an individual ‘tree’ of the random forest, the importance score of any variable used in constructing the tree is defined as the proportion of the training set that lies in the ‘leaves’ of nodes utilizing that variable (variables not used in constructing the tree are assigned a score of zero); then the overall importance score for a variable is the average of its importance scores on each tree.

For different biological families of proteins (the same as those used in FIGS. 3A-F), we calculated the overall importance in discriminating different cancer types (FIG. 10A, (a)-(c)). The results suggest that different families of proteins are important in detecting different cancers. For example, acute phase proteins were relatively important in detecting meningioma, and lipoproteins were relatively important in detecting glioblastoma. Notably, these variations were distinct from the variations in the percentage of each category adsorbed onto the liposomes (FIG. 10A, (d)-(f)). Interestingly, these results are in good agreement with the biological function of these protein categories. For example, it is well-accepted that lipid metabolisms are substantially altered in glioblastoma compared to the healthy tissue, which may be the main reason for the observed substantial changes in the interaction of lipoproteins with liposomes (FIGS. 2C and 10A). Details on the numbers of identified proteins and unique proteins in the corona composition of different liposomes and their combinations are provided FIG. 10B.

We also calculated the most important overall proteins (FIG. 10C and Table 5). These proteins were detected in combinations of all three liposomes, again showing the critical role of multi-liposomes in the nanosystem. We also evaluate the robustness of this set of ‘important’ proteins across the classifiers estimated on the 1000 splits of training data discussed earlier. Specifically, FIG. 10B shows the 25th to 75th percentiles of the importance scores for the 30 most important proteins on average. These show that the set of important proteins is robust to the split of data used for model training. Among these most important proteins (see Table 5), some have been recognized as playing critical roles in cancer development. For example, Ficolins (both Ficolin 2 and Ficolin 3) are serum pattern recognition molecules with opsonic properties with a substantial capacity to regulate complement activation. The serum concentrations of Ficolin 3 have been demonstrated to be higher in patients with ovarian cancer than in healthy subjects. Moreover, Ficolin 3 was identified in a differential proteomic analysis of prostate cancer serum, suggesting a role for this protein in prostate cancer as well. On the other hand, it is well established that Apolipoprotein A2 and its isoforms are overexpressed in prostate cancer serum and that the concentration of acute-phase proteins (e.g., complement proteins) can change by 25% in the presence of inflammatory disorders such as cancer. A clear association between cancer and the hemostatic system has long been documented. Hemostasis modulates blood flow by regulating the adhesion of platelets and deposition of fibrin. Several proteins involved in hemostasis have been connected to the regulation of angiogenesis. Among these, fibrinogen is the main protein in the hemostasis process and has been found in many tumors; it modulates angiogenesis and tumor growth and has been implicated in metastasis formation. Indeed, plasma levels of fibrinogen have been used to forecast clinical outcomes in patients with non-metastatic renal cell carcinoma, and to predict distant metastasis in pancreatic cancer.

TABLE 5 Information about the most important overall proteins, found to be detected on combinations of all three liposomes. Uni- pro- tentry Protein Amount in name description Function plasma* FCN3 Ficolin-3 complement activation, 1 μg/ml lectin pathway SAA4 Serum amyloid chemoattractant activity 30 μg/ml A-4 protein CBPN Carboxy- protects the body from 720 ng/ml peptidase vasoactive and N catalytic chain inflammatory peptides containing C-terminal Arg or Ly APOA2 Apolipoprotein acute inflammatory 750 μg/ml A2 response, lipid transport CO7 Complement regulator of innate and 2.6 μg/ml component C7 adaptive immune response FHR5 Complement complement activation, 11 ng/ml factor H-related alternative pathway protein 5 COF1 Cofilin-1 actin cytoskeleton 140 ng/ml organization HABP2 Hyaluronan- serine-type 1.1 μg/ml binding protein 2 endopeptidase activity IGHG1 Immunoglobulin antigen binding N.A. heavy constant gamma 1 IGHG3 Immunoglobulin antigen binding N.A. heavy constant gamma 3 IGHG2 Immunoglobulin antigen binding N.A. heavy constant gamma 2 RET4 Retinol-binding retinol transporter 580 μg/ml protein 4 VTNC Vitronectin cell adhesion 35 μg/ml GRP78 78 kDa glucose- ATPase activity 100 ng/ml regulated protein KV118 Ig kappa chain Antigen binding N.A. V-I region WEA CPN2 Carboxy- regulation of 2 μg/ml peptidase complement activation N subunit 2 COL11 Collectin-11 mannose binding, N.A. complement activation MASP1 Mannan-binding complement activation, 240 ng/ml lectin serine lectin pathway protease 1 FIBB Fibrinogen beta hemostasis 706 μg/ml chain FIBA Fibrinogen alpha hemostasis 2.5 mg/ml chain C1S Complement C1s regulation of 50 μg/ml subcomponent complement activation FGL1 Fibrinogen-like hemostasis 2.3 ng/ml protein 1 VWF von Willebrand hemostasis 110 μg/ml factor CO6 Complement regulation of 40 μg/ml component C6 complement activation IGHA1 Immunoglobulin antigen binding N.A. heavy constant alpha 1 IGLL5 Immunoglobulin antigen binding N.A. lambda-like polypeptide 5 CO8A Complement regulation of 70-90 component C8 complement activation μg/ml alpha chain K1C14 Keratin, type I structural constituent 210 ng/ml cytoskeletal 14 of cytoskeleton CRP C-reactive complement activation, 2 μg/ml protein classical pathway CO8G Complement regulation of 1.1 μg/ml component C8 complement activation gamma chain *The concentrations are values obtained using spectral counting from the plasma proteome database (see website at plasmaproteomedatabase.org).

To further probe the role of the important proteins identified by our machine learning approach, we searched for them in the Open Targets database, a platform for therapeutic target identification and validation. That database calculates a disease-association score for each protein based on evidence from various other databases (including GWAS Catalog, UniProt, Gene2Phenotype, Cancer Gene Census, IntOGen, Europe PMC, and Reactome) to derive a score on a scale of 0 (lowest) to 1.0 (highest) of disease association. Of the proteins listed, three have strong associations with cancers. Hyaluronan Binding Protein has a very strong general association (1.0) with cancers; Fibrinogen Beta Chain has a moderately strong association (0.4) with lung cancer; while Keratin, Type 1 cytoskeletal 14 is strongly associated (0.72) with prostate cancer. Almost all the other proteins in Table 5 have some degree of weak association (0.05-0.4) with various types of cancers. Hence, overall, the proteins have a linkage with known cancer associations.

Overcoming Variability in Single Measurements with Tensor Factorization

Due to significant variability in patient populations, along with noise introduced through measurement error, we found that any single protein was insufficient for classification. For each of the 100 most-abundant proteins (yielding 3*100=300 variables), we calculated the average absolute z-score of that proteins concentration in the observed corona across patients of each cancer type. A higher z-score for a cancer type on a given protein indicates that this protein may be useful in detecting this cancer type. FIG. 11 (blue bars) shows a histogram of these average absolute z-scores for each cancer type and the healthy group. We also measured average absolute z-scores for proteins previously linked to these specific cancer types, which are displayed in the same histogram in FIG. 10 (light grey bars). Across all of these hundreds of variables, only a single protein has an absolute z-score above 2.0, and on only a single cancer type (Myeloma), suggesting that no single protein suffices for accurate classification.

The tensor decomposition that precedes our construction of a random forest effectively serves the role of computing a small number of weighted averages of protein composition in the observed corona on a given sample. This average is across all proteins and nanoparticles in a given plasma sample, and serves the role of mitigating the variability in the observed concentration of any given protein. For example, in FIG. 11 (long, black bars), the average absolute z-score for one of these weighted averages is plotted for each cancer type. The absolute z-scores of these weighted averages are significantly higher than those of any single variable. In addition to the intuition this provides for how our approach overcomes variations in a single protein across samples with the same indication, this de-noising also materially impacts our ability to classify. Absent de-noising, simply training a random forest classifier on the raw corona data would yield a classification accuracy of 94% (at a p-value of 0.07) as opposed to 96.2% (at a p-value of 0.04) reported in Table 4. For the cohort data reported in Table 7 de-noising enabled us to increase classification accuracy from 92% (at a p-value of 0.04) to 94.1% (at a p-value of 0.01).

Dependence of Classification Accuracy on Data

Our final evaluation on the 45 non-cohort patients was of the value of data. Our original classifier was trained on 5 samples per cancer type. To measure the value of including more or less training data, we repeated the classification procedure (splitting the data into training and testing samples, training a classifier on the training samples, and measuring performance on the testing samples, all done 1000 times) for a varying number of training samples per class, ranging from four to six (Table 6. Classification accuracy, sensitivity, and specificity all increased with increasing numbers of training samples. With six training samples per class, overall accuracy reaches 96.8% (i.e. an overall error rate of 3.2%). This strongly suggests that accuracy, sensitivity, and specificity will continue to increase as more data are included in training the classifier.

TABLE 6 Classification accuracy improves with more data. (Column 2) Overall classification error when the training set consists of four, five, and six samples from each cancer, and associated p-values. Both classification error and the associated p-values improve with additional samples from each cancer. (Columns 3-12) Sensitivity and specificity for glioblastoma, lung, meningioma, myeloma, and pancreatic cancers when the training set consists of four to six samples. Experimental results are averaged over 1000 independent draws of a training set with four healthy patients, and four to six patients with each cancer type. p-values are for the null hypothesis of at least two classification errors. # Glioblastoma Lung Meningioma Myeloma Pancreatic Samples Accuracy Sens. Spec. Sens. Spec. Sens. Spec. Sens. Spec. Sens. Spec. Four 94.4 (0.14) 98.8 98.1 91.2 100.0 93.0 96.7 100.0 99.9 88.0 98.4 Five 96.2 (0.04) 100.0 98.9 94.0 100.0 98.5 97.0 100.0 100.0 87.4 99.5 Six 96.8 (0.01) 100.0 99.4 96.6 100.0 98.9 97.0 100.0 100.0 87.8 99.6 Sampling of Low- and High-Abundance Plasma Proteins with Liposomes without the Requirement of Protein Depletion

The multi-liposome protein corona nanosystem, using machine-learning techniques, produces a unique “fingerprint” protein pattern for each type of cancer and for healthy individuals. In pursuit of the mechanism underlying the unique capacity of the protein corona in cancer identification and discrimination, we have thoroughly analyzed the corona composition for the contribution of both high- and low-abundance proteins, and compared those outcomes with the concentration of corona proteins in human plasma. In this regard, the contribution of each protein (e.g., protein X) to the corona composition and plasma was normalized with respect to albumin using (total peptides of albumin in protein corona)/(total peptides of protein X in protein corona) and (concentration of albumin in plasma)/(concentration of protein X in plasma), respectively. It is noteworthy that we manually searched the concentrations of identified corona proteins in plasma using an online proteome database (see website at plasmaproteomedatabase.org. As the total peptides of the albumin in the protein corona are proportional to albumin's total weight in the protein corona, dividing these peptides to the peptides of protein X is comparable with the ratio of albumin concentration to concentration of protein X in plasma. As shown in FIG. 12 , we found that the plasma concentrations vary over 10 orders of magnitude (in log-log scale), while the liposomes detect these same proteins over 4-5 orders of magnitude. In other words, we revealed that the protein corona composition has a great capacity to concentrate a wide range of low-abundance proteins (100 ng/mg) and very rare proteins (10 ng/mg). This means that obtaining data on highly abundant proteins in the protein corona does not interfere with detection of peptides derived from less-abundant and rare proteins. It is worth noting that most of the detected proteins are low-abundance, rare, or unknown/unreported proteins. Participation of the low-abundance proteins in the corona composition is mainly due to the exchange of corona proteins with low affinity for proteins with higher affinity and slower adsorption kinetics.

Detection of low-abundance proteins in human plasma requires depletions of highly abundant proteins and post-depletion plasma-fractionation strategies; however, even using these depletion strategies, plasma proteomics has not been robustly successful in early detection of cancers. The results obtained with our system indicate that, in contrast to human plasma proteins, the protein corona composition contains a wide range of less-abundant and very rare plasma proteins, without need for depletion (which may cause unintended removal of low-abundance proteins/biomarkers). In addition, we found several proteins in the protein corona whose concentrations in human plasma are unknown/unreported, possible due to their very low concentration in human plasma. More specifically, anionic, neutral, and cationic liposomes account for 323, 189, and 155 of proteins with unknown/unreported plasma concentration, respectively). The contribution of these proteins to the protein corona is indicated by the rectangular box on the right in FIG. 12 .

The use of multi-liposomes (with distinct surface properties) provides a unique opportunity to increase the detection depth of the low-abundant proteins and very rare proteins (see FIG. 12 ), which substantially enhanced the sensitivity, specificity, and predictive accuracy of the protein corona nanosystem. Each liposome provided different patterns of contributed proteins with a strong dependency on cancer type.

Cancer Detection and Discrimination Among Cohort Samples

Finally, to investigate the ability of the protein corona nanosystem to detect cancers at very early stages, we used cohort plasma (obtained from the NIH-funded Golestan Cohort Study; details are provided in the Methods section) from healthy people who were diagnosed several years after plasma collection with pancreatic, lung, and brain cancers. We followed the same procedure, performing 1000 experiments. In each experiment, we partitioned the data into 12 (4 each from 3 cancer types) training samples and 3 testing samples (one each from 3 cancer types). Observations were denoised via the previously described procedure, and then a random forest classifier was trained on the training samples. Finally, overall accuracy, sensitivity, and specificity were measured on the test samples (Table 7). Overall accuracy was 94.1% (an error rate of 5.9%), with a p-value of 0.01 for the null hypothesis of an overall accuracy <66.7% (thus rejected with 95% confidence). Sensitivities across the three cancer types ranged from 83.2% to 100.0%, and specificities ranged from 91.6% to 100.0%. These relatively high values suggest that the protein corona array can successfully detect cancers at their earliest stages.

TABLE 7 Overall Classification Accuracy, Sensitivity, and Specificity for Cohort Samples. (Column 2) Overall classification accuracy for one, two, and three liposomes. Both classification error and the associated p-values improve with the addition of liposomes to the nanosystem. (Columns 3-8) Sensitivity and Specificity for Brain, Lung, and Pancreatic cancers, respectively. Again, sensitivity and specificity improve with the addition of liposomes. Experimental results are averaged over 1000 independent draws of a training set comprising 12 patients, with evaluation of the remaining 3 patients. p- values are for the null hypothesis of a classification accuracy <66.7%. Array Brain Lung Pancreatic Size Accuracy Sens. Spec. Sens. Spec. Sens. Spec. One 75.4 (0.23) 74.7 86.1 90.7 90.9 60.8 86.9 Two 80.5 (0.11) 92.3 89.7 76.3 92.1 73.1 88.9 Three 94.1 (0.01) 100.0 100.0 83.2 99.6 99.2 91.6

DISCUSSION

No prior study using protein corona or any other approach for fractionation of the plasma proteome has enabled concurrent multi-cancer screening with acceptable specificity, sensitivity, and predictive accuracy. This is the first time a sensor array has been developed with the specificity, sensitivity and predictive accuracy for not only cancer, but specific cancer subtypes.

The fractionation of the plasma proteome by the protein corona has been demonstrated to be unrelated to the abundance of specific plasma proteins and occurs instead via many factors including protein affinity for the nanoparticle surface through a wide range of forces including Coulomb forces, London dispersion, hydrogen-bond acidity and basicity, polarizability, lone-pair electrons, and protein-protein interactions between participating proteins in the corona structure. Protein corona composition has been shown to be dynamic and initially dominated by abundant proteins including albumin, immunoglobulin, and fibrinogen, which together with 19 other proteins comprise over 99% of the protein mass in the plasma proteome. The remaining 1% of the plasma proteome is comprised of over 10,000 proteins; a subset of these proteins with higher affinities and/or lower absorption kinetics for the nanoparticle surface compete with the high-abundance proteins for inclusion in the corona composition. In addition to the exchange of the proteins with higher binding affinity for those with lower binding affinity at the surface of nanoparticles, there is a chance for a contribution by other low-affinity proteins in the outer protein corona layer due to their favorable protein-protein interactions with the already-formed protein corona layer. This means that the exchanged low-abundant proteins may be able to direct the formation of the protein corona toward adsorption of more low-abundance proteins.

Herein we analyze for the first time the relative concentration capacity of the protein corona in enriching low-abundance proteins (defined as <100 ng/ml), demonstrating that many of these proteins are at concentrations <10 ng/ml and approaching 1 pg/ml. More importantly, we show that many of these proteins play a crucial role in cancer identification and discrimination via machine-learning approaches. The role of the protein corona in concentrating a wide range of low-abundance and very rare proteins may go a long way towards overcoming the main reasons behind the limited success of current mass spectrometry techniques (including LC-MS/MS) in early detection of cancers, as these techniques can detect proteins at a dynamic range of 4-6 orders of magnitude. In other words, the protein corona composition enables sampling across a vast dynamic range of the plasma proteome, which can substantially enhance the depth of protein coverage without protein depletion. Since the protein corona obtained from a single nanoparticle constitutes at most several hundred distinct proteins (a small subset of the total proteome), we postulated that using multi-nanoparticles with distinct physiochemical properties might create additional dimensions of proteomic information: 1) each additional nanoparticle with distinct physicochemical properties potentially enables the recruitment of additional unique low-abundance proteins (FIG. 12 ); 2) corona proteins that overlap more than one nanoparticle surface participate at different corona contribution percentages, and thus alter the concentration and identity of other participating corona proteins; and 3 rd) both unique and overlapping corona protein information from each nanoparticle serve as unique variables, and therefore provide more data to our machine learning approach. Combining more nanoparticles for plasma fractionating and proteomic analysis provides significantly more information for cancer detection and discrimination with superior sensitivity, specificity, and prediction accuracy compared to fewer nanoparticles (Table 4). Conceptually, our multi-nanoparticle approach is similar to the olfactory system, in which the specificity of odorant recognition originates from the pattern of responses from several hundred highly cross-reactive olfactory receptors, where any one receptor provides incomplete information but the combination is highly specific in identifying a given odorant (i.e., in humans ˜400 active receptors can detect and differentiate ˜10,000 odorants, and in dogs ˜1200 active receptors can detect ˜1,000,000 odorants). Similar approaches have also been used by other investigators to detect and differentiate among diverse families of analytes, various foods and beverages, pathogenic bacteria and fungi, biomolecules, and even nanoparticles themselves.

Three different cross-reactive liposomes (with negative, neutral, and positive surface charges) were used whose protein corona profiles were measured after exposure to the plasma of individual patients who had one of five cancers: lung, pancreas, myeloma, meningioma, or glioblastoma. To identify and discriminate among cancers using the protein corona nanosystem outcomes, we used a well-defined random forest machine learning approach. We have designated 1000 different sets of samples as training (i.e., plasmas with known cancers and healthy conditions) or testing (i.e., blind plasmas) samples to ensure that our protein corona nanosystem is robust and accurate for cancer detection with excellent predictive accuracy. Although no one protein corona composition from a single nanoparticle was specific for any particular cancer type with acceptable predictive accuracy (i.e., 86.0% with p-value of 0.43 for the classification error lower than 87.5%), we found that the pattern of corona composition derived from the multi-liposomes provides a unique “fingerprint” for each type of cancer with excellent predictive accuracy (i.e., 96.2% with p-value of 0.04 for the classification error lower than 87.5%). These results, based on the deep analysis of the human proteome using multi-liposome protein corona characterization and machine learning, confirmed the promise of this system for unambiguous identification and discrimination of cancers and error-free discrimination against healthy subjects with excellent specificity (from 97.0% to 100.0%).

To probe the capacity of the protein corona nanosystem for very early detection of cancers, cohort plasma samples were used. These samples were collected from healthy people who were diagnosed with lung, pancreas, or brain cancer eight years after plasma collection. The outcomes of the protein corona nanosystem, using plasma from 15 patients in the cohort study, revealed that our approach accurately identified and discriminated cancers even in these pre-diagnosis cohort samples, for which cancer detection was not possible with current alternatives. In agreement with our findings on the fresh plasma samples, multi-liposome plasma sampling provided superior classification accuracy (94.1% vs. 75.4%) and specificity [i.e., brain (100.0% vs. 86.1%) lung (96.6% vs. 90.9%), and pancreatic (91.6% vs. 86.9%)] compared to single-liposome sampling. It is noteworthy that the protein corona profiles of the cohort samples were different compared to the previous fresh cancer samples. This is mainly because of the long-frozen storage (around 10 years) of the cohort samples, as the samples were collected at the time of screening of healthy individuals. It is increasingly accepted that long-term storage of plasma samples can strongly affect the concentration and integrity of a subset of proteins, in turn altering the protein corona composition and decreasing the sensitivity of our protein corona nanosystem. Therefore, the maximal sensitivity of the nanosystem may be realized when using fresh plasma, either as part of a cancer screening or cancer work-up after diagnosis. The value in the latter setting may be that changes in the protein corona pattern over time may provide valuable information relevant to early tumor recurrence or the presence of residual disease after tumor resection.

In summary, we present proof-of-concept that the multi-nanoparticle protein corona nanosystem has considerable potential for increasing the depth of protein detection and thus a unique capacity to accurately detect and discriminate cancers even at their earliest stages, when existing technologies fail to detect disease. The multi-nanoparticle protein corona pattern derived from our protein corona nanosystem provides a unique multivariate “fingerprint” for cancer detection, which is not possible when the protein corona of only a single nanoparticle is analyzed. Furthermore, the protein corona pattern represents the collective enrichment of a wide range of plasma proteins (including both abundant and rare proteins) using distinct nanoparticles, clearly distinguishing it from other multivariate whole-plasma proteomic approaches that have failed to produce suitable results for early cancer detection. The depth of protein detection (the main limitation of protein analysis in human plasma) and predictive accuracy of the nanosystem may be further enhanced by using additional nanoparticles with different physicochemical properties. The successful predictive outcome of our machine-learning and protein-corona characterization approach for both blind fresh plasmas and retrospective cohort plasmas provides a suitable foundation for subsequent prospective studies in cancer. Furthermore, the utility of the multi-nanoparticle protein corona nanosystem can be applied to other important human diseases for which early detection can significantly improve both longevity and quality of life.

Liposomes were prepared as described in Example 1A.

Human plasma collection, preparation, and storage was performed as described in Example 1A.

Cohort plasma samples were prepared as described in Example 1A.

Transmission electron microscopy (TEM). Liposome formulations have been characterized by TEM as reported previously. Briefly, 10 μl of each sample was deposited onto Formvar-coated grids, negatively stained using 1% uranyl acetate, washed with ultrapure water, and air-dried. Measurements were performed with a Zeiss Libra 120, and image analysis was performed with Image) software.

Size and zeta-potential was determined as detailed in Example 1A.

Protein assay was carried out as described in Example 1A.

Protein identification and quantification was performed as in Example 1A. Unweighted spectrum counts (USC) were used to assess the consistency of biological replicates in quantitative analysis, and normalized spectrum counts (NC S) were used to retrieve protein abundance.

Statistical Analysis. All statistical analyses in the main text were performed in Python using the scikit-learn, numpy, and scipy packages, and figures and graphs were created using the bokeh package in Python, along with Microsoft Excel, XLSTAT, and MATLAB.

Data matrices. For all 60 plasma samples (45 non-cohort and 15 cohort), labeled as i=1, . . . ,60, a data matrix X_(i) (with 3 rows and ˜900 columns) was generated such that each row of the matrix corresponds to the protein abundances of a single nanoparticle, as obtained from the protein corona nanosystem. As a preprocessing step, we converted the protein abundances to relative protein abundances (RPA) by normalizing the rows of all of the matrices.

Classification and Clustering

Tensor factorization. We treated the data as a three-mode tensor, the first two modes corresponding to nanoparticles and proteins, and the third mode corresponding to plasma samples; this is essentially equivalent to stacking the observation matrices corresponding to each sample, X_(i), on top of each other. The data were de-noised via a low Tucker rank tensor factorization (135,136,137) using code implemented in Python for this project (available for academic use upon request). Each matrix X_(i), is approximated by a tensor decomposition that takes the form

X _(i) ˜US _(i) V ^(T),

where U is a matrix whose rows can be viewed as latent features corresponding to each of the nanoparticles, and similarly V is a matrix whose rows can be viewed as latent features corresponding to each of the proteins; these latent features are shared across all of the data matrices. Finally, each S_(i) is a matrix encoding interactions between nanoparticle and protein features, and these are allowed to be unique between samples. We estimated this decomposition in two steps: we (a) estimated U and V via a truncated singular-value decomposition on the mode-1 and mode-2 unfoldings of the tensor, and then given these estimates, we (b) fit each S_(i) matrix separately via a least-squares calculation.

Random forest classification. The random forest model is a well-known machine learning algorithm for classification. A random forest is made up of multiple decision trees that each make simple classification decisions based on relatively few variables. These trees are created (or “trained”) with different, randomly drawn subsets of variables so that it is likely that no two trees are identical. Given a new sample, each tree is traversed top-down until a set of training samples is reached at the bottom. Using the forest as a whole for classification amounts to having the multiple decision trees “vote” on a label (in this case, one of five cancer types, or healthy), where each tree's vote is made from the labels of the bottom set of training samples. For our own algorithm, each random forest consisted of 1000 decision trees and was trained using the scikit-learn package. Importance scores were also calculated using the same package.

Example 2. Additional Sensor Array Construction for Detection of Diseases

A sensor array consisting of 12 different cross-reactive nanoparticles including three liposomes, three superparamagnetic iron oxide nanoparticles, and six gold nanoparticles are made. These types of liposomes (DOPG (1,2-dioleoyl-sn-glycero-3-phospho-(1′-rac-glycerol)), DOTAP (1,2-Dioleoyl-3-trimethylammonium-propane)-DOPE (dioleoylphosphatidylethanolamine), and CHOL (DOPC-Cholesterol)) with negative, neutral, and positive surface charges are synthesized according to our previous reports. Ultra-uniform PEG-coated superparamagnetic iron oxide nanoparticles 20 nm in size and of various PEG molecular weights (i.e., 300, 3000, and 6000) are obtained from Micromod®. Gold nanoparticles, with core size of ˜2 nm, and different surface functionalities are synthesized.

All of the nanoparticles are the same size but have different surface properties, which are expected to form significantly different protein corona compositions in response to the plasma of patients developing various types of cancers. The sensor array probes the capability of the protein corona sensor array to identify and discriminate among cancer types via the patient's plasma proteins, as described in Example 1.

Samples from a wide range of cancers including lung, pancreas, myeloma, meningioma, glioblastoma, esophageal squamous cell carcinoma, and gastric adenocarcinoma are probed. Protein corona arrays based on different nanoparticles (liposomes, iron oxide, and gold) are designed to probe the variation in biomolecule fingerprint among various cancer types. The sensor assay will also allow for the identification of proteins that are markers for specific types of cancers, including new and unknown biomarkers for different cancer cell types. The pattern recognition that can be determined based on the different types of cancer or the stage of cancer.

A wide range of human plasmas from healthy people that were later diagnosed with various types of cancers several years after plasma collection will be analyzed. The plasma samples were collected through a NIH-funded cohort study, named the Golestan Cohort Study, performed by the National Cancer Institute (NCI) in the USA, the International Agency for Research on Cancer (IARC) in France, and the Tehran University of Medical Sciences (TUMS) in Iran. This study involved the collection and storage of plasma from 50,000 healthy subjects. Over 1,000 of these subjects went on to develop various types of cancers in subsequent years. The samples are stored at IARC and being used by our team for analysis. These important plasma samples provide us a unique opportunity to probe the capacity of our innovative protein corona sensor array for early detection of cancers. In addition, we will also assess and identify proteins useful for the identification and discrimination of these cancers.

We believe that the outcomes from applying this innovative sensor array to cohort plasma samples will not only be instrumental in the detection and screening of cancers at early stages but also help identify novel protein markers involved in cancer development. Our sensor array component choices have more specific capability compared to other developed methods to provide fingerprints for a wide variety of proteins in a non-specific, cross-reactive manner for identification and discrimination of cancers.

The Hard Corona Profiles of the Sensor Array Elements are Probed Using Plasma from Patients with Cancers at Intermediate and Advanced Stages:

The composition of the protein corona that forms on the surface of sensor array elements is strongly dependent on the physicochemical properties of those nanoparticles and, at the same time, can be strongly affected by the type of disease present in the donor of the human plasma used for incubation. To prepare the corona-coated nanoparticles, the 12 nanoparticles prepared are incubated with human plasma (separately) of nine types of cancers (lung, pancreas, myeloma, myeloid leukemia, meningioma, glioblastoma, breast, esophageal squamous cell carcinoma, and gastric adenocarcinoma) and isolated from free proteins via a well-defined centrifugation approach. Centrifugation is usually performed at 13000 g for 30 min at 15° C. The supernatant will be removed and the collected particles would be re-dispersed in 500 microlitter of PBS. The procedure will be repeated to get the loosely attached proteins removed. In order to remove the loosely attached proteins from the surface of nanoparticles, the collected nanoparticles will be redispersed in cold PBS (15° C.) and collected via centrifugation. The size and charge of the corona-coated nanoparticles will then be determined using DLS/Nanosight and compared to their initial values obtained in buffer. Quantitative evaluation of the total protein adsorbed onto the nanoparticles will be performed via the BCA or NanoOrange assay, while qualitative shotgun proteomics analysis identify the proteins adsorbed onto the surface of the 12 nanoparticles. Briefly, after separation of proteins from the surface of nanoparticles (according to the protocol (Saha, K.; Rahimi, M.; Yazdani, M.; Kim, S. T.; Moyano, D. F.; Hou, S.; Das, R.; Mout, R.; Rezaee, F.; Mahmoudi, M. ACS nano 2016, 10, (4), 4421-4430, incorporated by reference), proteins are injected into a liquid chromatography-mass spectrometry (LC-MS/MS) apparatus. The proteins are identified from the resulting data through screening of relevant databases. To obtain the total number of LC-MS/MS spectra for all peptides attributed to a matched protein, semi-aPolydispersity index from cumulant fitting quantitative assessment of the protein amount will be conducted through spectral counting (SpC). The normalized SpC (NpSpC) amounts of each protein identified in the LC-MS/MS spectra will be calculated using the following equation:

${NpSpCk} = {\left( \frac{\frac{SpC}{\left( M_{w} \right)_{k}}}{{\sum}_{t = 1}^{n}\left( \frac{Spc}{\left( M_{{w)}_{t}} \right.} \right)} \right) \times 100}$

where NpSpCk is the normalized percentage of spectral count (i.e., raw counts of ions) for protein k, SpC is the spectral count, and Mw is the molecular weight (in kDa) of the protein k.

Develop Supervised and Unsupervised Clustering Analysis to Identify and Discriminate Among Cancers Using the Sensor Array Outcomes:

In order to investigate whether protein corona fingerprints (PCFs) of various sensor elements could be utilized as a biosensors and form unique patterns for different diseases (biomolecule corona signature), we have applied focused classification approaches to proteomic data from three liposomes' protein corona composition (cationic, anionic, and neutral) as described in Example 1.

Example 3. Conjugation of Nanoparticles to the Substrate to Make Sensor Arrays

Different types of particles may be used as nanoscale sensor elements in the practice of this invention. Further, different methods of conjugation of the nanoscale sensor elements to the substrate are provided. Additionally, the nanoscale sensor elements may be attached to substrate in different patterns.

Specific examples of different configurations of sensor elements on different substrates are exemplified in FIG. 15-43 .

Example 4. Sensor Array Comprising Silica and Polystyrene Nanoparticles for Screening for Cancer

This Example demonstrates that a sensor array of the present invention with different nanoparticles than those used in Example 1 is still able to detect cancer samples from healthy patient samples.

Utilizing the experimental protocol of Example 1, a sensor array was designed using functionalized silica and polystyrene particles. In this Example, a total of six nanoparticles: two nanoparticles types, i.e. polystyrene (P) and silica (S), with three different surface functionalization, i.e. none, amine modification and carboxyl modification (P—NH2, P—COOH, S—NH2 and S—COOH), were used.

Characterization of bare polystyrene and silica nanoparticles with different functionalization (none, amine modification (NK2) and carboxyl modification (COOH) is shown in FIGS. 44A-44D demonstrating their sizes, DLS and zeta potential of the bare particles and TEM images. The characterization of protein corona-coated polystyrene and silica nanoparticles with different functionalization is demonstrated in FIGS. 45A-45D with their sizes, DLS, zeta potential and TEMs of the protein-corona loaded polystyrene and silica nanoparticles.

The 6 nanoparticle sensor array was contacted with the plasma of healthy individuals or patients with rectum cancer, breast cancer, bladder cancer, thyroid cancer, uterus cancer, ovary cancer, kidney cancer (5 patients per cancer) as depicted in FIG. 46 by the method described in Example 1. The protein corona profiles of polystyrene and silica nanoparticles (100 nm) were analyzed by SDS PAGE. Comparison of the protein corona of plain, amine-modified and carboxyl-modified particles by SDS PAGE is shown in FIG. 47 .

The protein corona profiles for healthy plasma for polystyrene and silica nanoparticles (100 nm) analyzed by SDS-PAGE is shown in FIG. 48 . Comparison of the protein corona of plain, amine-modified and carboxyl-modified particles.

The data was analyzed as described in Example 1. The statistical analysis and clustering results are depicted in FIG. 49 . As depicted, the healthy individuals are able to be identified and classified as compared to the cancer patients (healthy controls are in the orthogonal space vs the cancer patient samples as seen in FIG. 49 ).

This Example demonstrates that this sensor array using a six nanoparticle array can discriminate and detect a patient with cancer from a healthy individual.

Materials: Three differently functionalized silica particles were purchased by Kisker-Products (see website at kisker-biotech.com); three differently functionalized polystyrene particles were purchased by Polyscience, Inc. (see website at polysciences.com). All the particles had the same size (100 nm). Their morphology, average size, polydispersity index (PDI) and zeta potential were characterized by TEM, DLS and zeta potential measurements.

Experimental info: 1 h incubation in 50% human healthy plasma. SDS PAGE: 4-20% acrylamide 45 min 40 mA/gel. Staining: Colloidal Blue Comassie overnight. nanoparticles used: 0.5 mg).

Example 5. Protein Corona Sensor Array Nanosystem Identifies Coronary Artery Disease

Coronary artery disease (CAD) is the most common type of heart disease and represents the leading cause of death in both men and women. Early detection of CAD is crucial in preventing death, prolong the survival and ameliorate quality of life of patients. This Example describes the non-invasive, sensor array nanosystem containing six nanoparticles for ultraprecise detection of CAD using specific PC pattern recognition. While the PC of a single nanoparticle do not provide the required specificity, the multivariate PCs across six distinct nanoparticles with different surface chemistries provides the desirable information to selectively discriminate each cardiovascular condition under investigation.

CAD is a chronic condition which starts during adolescence and progresses gradually throughout the affected person's entire life. It is characterized by the presence of atherosclerotic plaques in the coronary arteries. The genesis of atherosclerosis lies in the dysfunction of the endothelium: when subjected to stress stimuli and inflammatory factors (e.g. oxidative stress and hemodynamic forces), endothelial cells express surface adhesion molecules inducing the recruitment of circulating leukocytes and low density lipoproteins (LDL) containing cholesterol.⁵ These events induce the formation of the atherosclerotic plaques, which narrows the coronary artery and thus impairs the blood flow. Depending on the velocity of the plaque's development and on the severity of the artery obstruction, the symptoms can culminate in myocardial infarction.⁵

An accurate and in-time diagnosis of CAD in at-risk subjects is very important to promptly start an ad hoc therapy and avoid further complications. Coronary angiography is to date the most accurate and trustable method for CAD diagnosis. However, inserting a catheter into an artery of the arm (or neck or upper tight) up to the heart is invasive, costly and causes many side effects, including infections, injury to the catheterized artery, allergy and excessive bleeding. Therefore, there is an urgent need to develop new tests for CAD detection. While several inflammatory biomarkers have been reported as useful for diagnosis, unfortunately, however, none of them are used in clinical practice, highlighting the still very prevalent need for new diagnostic tests. The inventors have developed a nano-based blood test as a new tool for diagnosis of CAD.

As demonstrated in the previous Examples for cancer, personalized PCs act as fingerprint of a given plasma condition. This Example uses the same approach to accurately define the formation of the atherosclerotic plaque, through its induced changes in plasma composition. Indeed, the plaque-associated cells (e.g. foam cells, macrophages, mast cells, monocytes, and T-cells) shed a wide range of biomolecules (e.g., cytokines, proteases, and vasoactive biomolecules) to the blood,²² and thus may induce changes in the pattern of PC composition at the surface of various nanoparticles in respect to the PC of patients with no plaque formation.

This Example analyzed the PC formed around nanoparticles using plasma derived from i) patients who are diagnosed with CAD following coronary angiography (CAD), ii) patients with symptoms who had coronary angiography and their coronary vessels were found healthy (NO CAD), iii) restenosis (recurrence of CAD after treatment) and iv) healthy volunteers with no risk factors (e.g. family history, tobacco use, obesity, hypertension) for cardiovascular disease (CONTROL).

In order to have a wider spectrum of adsorbed proteins, the Example used six commercially available nanoparticles as the sensor array elements, with different composition and surface chemistry and/or functionalization, creating a 6 nanoparticles PC-based sensor array able to be used as an easy and non-invasive diagnostic test. This novel diagnostic CAD test to be used as pre-non-invasive screening for at-risk patients. Notably, these results demonstrated that PC patterns allowed the ultra-accurate discrimination between CAD, NO CAD, restenosis, and control patients, thus providing a novel, precise, non-invasive never developed before tool for blood-based diagnosis of CAD.

Results

In this Example, a total of six nanoparticles: two nanoparticles types, i.e. polystyrene (P) and silica (S), with three different surface functionalization, i.e. none, amine modification and carboxyl modification (P—NH2, P—COOH, S—NH2 and S—COOH), as described in FIG. 50 were used. The size, zeta potential and morphology of nanoparticles before and after incubation in plasma have been measured to compare differences in results between the synthetic identity of bare nanoparticles and their corresponding biological identity (PC-coated nanoparticles). Dynamic light scattering analysis showed that bare nanoparticles were all highly monodispersed, as demonstrated by polydispersity index 0.02, and homogeneous in size of about 100 nm, being in the range from 93 nm up to 120 nm (FIG. 50A). Following 1 h incubation with plasma of patients, sizes of all nanoparticles increased due to the presence of a layer of adsorbed proteins (PC), whose thickness and composition have been demonstrated to be dependent on protein concentration, surface properties and size of nanoparticles. All bare nanoparticles had negative surface charge (FIG. 50B), with those amine-functionalized slightly less negative than others due to the contribution of positive amine groups. These results were in line with specifications provided by the supplier and other studies. Modification with amine groups was not sufficient to switch the surface charge of silica and polystyrene nanoparticles characterized by all negatively charged residues on their surfaces at physiological pH.

Once exposed to plasma, all the surface charges became less negative (from −5 mV to −25 mV) due to the charge of most plasma proteins at physiological pH. Overall, the physicochemical properties of the PC-coated nanoparticles showed similar trends, being always bigger and less negative than their bare counterparts, irrespective of the plasma used for the incubation. However, when incubated with NO CAD plasma, P and S nanoparticles exhibited an increase in size of ≈85 nm, bigger than that showed using plasma of other conditions (40-50 nm). On the other hand, PC thickness of S—NH₂ nanoparticles incubated with CAD plasma was bigger (z 40 nm) than those derived from incubation of the same nanoparticles with other plasma types (z 30 nm). Transmission electron microscopy showed that nanoparticles did not change their morphology and structure after incubation in plasma (FIG. 50C). Furthermore, an increase in the size after coating was observed, thus confirming results obtained by dynamic light scattering. Protein concentrations of different PCs were evaluated by Bradford assay, showing that overall all silica nanoparticles adsorbed less proteins in the PC than polystyrene nanoparticles (FIG. 51A). This observation was confirmed through analysis of PCs by 1D-SDS PAGE. Five patients with CAD, NO CAD and no risk for CAD (CONTROL) have been used to collect plasma and the PCs obtained for all nanoparticles have been resolved onto Comassie stained SDS PAGE gels (FIG. 51B). Gels have been analyzed by densitometry and differences in the amount of proteins in the CAD, NO CAD and CONTROL PCs of the same nanoparticle have been detected (FIG. 51C, arrows). In some cases, we also noticed the presence and/or absence of some proteins in specific PCs (FIG. 51C, blue arrows). These results confirm that the formation of atherosclerosis plaque induces changes in plasma composition and, consequently, differences in PC. The protein corona were analyzed by LC-MS/MS analysis. More than 150 proteins have been identified in each PC-coated nanoparticle sample. In addition, spectral counting values, which represent the total number of fragmentation spectra for all peptides attributed to a specific protein, have been used to obtain information about the abundance of the proteins and, consequently, the percentage contribution of each identified proteins in the PCs. Differences in the percentage contribution of the top 20 abundant proteins in the PCs are reported in FIG. 52 . The results demonstrated correlation between the PC composition, the plasma condition, the type of nanoparticle and the surface functionalization.

Data obtained from all samples have been collected, analyzed and classified: a key for each measurement was created by concatenating nanoparticle, surface modification, type of plasma and label. Proteins identified with less than 2 peptides were removed from consideration and TIBCO Spotfire Analyst 7.6.1 was used to pivot the data so that rows were identified by protein accession, columns by the key and values containing the percentage contribution.

Besides mathematical analysis, we analyzed the presence of exclusive proteins in the corona of a given condition. To do this, we created Venn Diagrams which facilitate the research of common and unique proteins in big data set of proteins or genes. The PCs of each nanoparticle have been analyzed separately, for a total of 6 classifications. We looked for exclusive proteins by comparing proteins common to all 5 patients-derived PCs for CAD, NO CAD and control. Our results show that for each nanoparticle used in this study, various specific proteins are exclusively identified in specific PC patterns. Among these, several proteins involved in the regulation of complement activation (complement factor H related protein 3, complement component C8 gamma) were exclusively identified in the PC pattern of CAD patients. This result is in line with the recently described role of complement activation in the pathogenesis of cardiovascular diseases (development of atherosclerosis, plaque rupture, and thrombosis). Another example is represented by apolipoprotein (a), considered an attractive biomarker candidate for use into clinical practice for CAD, which we have detected exclusively in the PC pattern of CAD patients. Apolipoprotein (a) is the main component of lipoprotein (a), is well known to be subjected to proteolytical cleavage and its fragments accumulate in atherosclerotic plaques.

We confirmed the accuracy of the approach in discrimination of patients with CAD and NO CAD by analyzing 9 blind plasma samples (3 per each condition and 3 control). The PC was formed around the 6 nanoparticles of our PC sensor array nanosystem. Then, proteins in the PCs have been identified by LC-MS/MS (Supporting Information) and the results have been analyzed using the same classification and clustering approaches.

Statistical and data analysis is graphically represented in FIG. 54 showing the discrete isolation of the classification of the CAD, NO CAD and CONTROL (no risk of CAD).

In conclusion, we have demonstrated the accuracy of a 6 nanoparticles PC sensor array for the detection of CAD. The PC sensor array nanosystem developed in this work demonstrated to also be sensitive and accurate in the discrimination of CAD, restenosis, NO CAD, and healthy individual, which further showing its own great potential value as technology platform to be used in clinical setting. Indeed, despite the presence of many symptoms typically associated to atherosclerotic plaque, the NO CAD group of patients under investigation in this work did not have any obstruction in their arteries.

The PC patterns resulting from this platform represent a unique multivariate fingerprint, which is more accurate and broad-spectrum than those obtained using the PCs of a single nanoparticle. The approach presented here may be of great value for the detection of not only CAD, but also other various human diseases, improving many patients' quality of life. Especially due to the non-invasiveness of the test, we envision that such a test would be used more willingly and more frequently than angiography by patients. And unlike angiography, this test is easy to administer and has no side effects, allowing patients to check the status of arteries from the very first symptoms, and have significantly reduced CAD complications due to the early detection.

Methods

Nanoparticles. Three differently functionalized silica particles were purchased by Kisker-Products (see website at_kisker-biotech.com); three differently functionalized polystyrene particles were purchased by Polyscience, Inc. (see website at polysciences.com). All the particles had the same size (100 nm). Their morphology, average size, polydispersity index (PDI) and zeta potential were characterized by TEM, DLS and zeta potential measurements.

Protein corona formation. The PCs were created by incubating 0.5 mg of nanoparticles in deionized H₂O with the same volume of human plasma. Incubation was performed in 37° C. under agitation for 1 h. Immediately after incubation, centrifugation was executed at 14,000 rpm and 10° C. for 30 minutes to form a pellet. Next, the pellet was washed and suspended in 200 μl of phosphate-buffered saline (PBS) at 4° C. The centrifugation measures were repeated three times under the same previous conditions. The pellet of the PC-coated nanoparticles was resuspended in 8M Urea, 50 mM ammonium bicarbonate to later run SDS-PAGE gels and LC/MSMS analysis or in deionized H₂O to later analyze the size and ζ-potential.

Nanoparticles characterization. Size and ζ-potential of bare and protein corona-coated nanoparticles have been characterized by diluting 10 μl of each sample in 1 ml total of distilled water. Measurements have been performed using a Zetasizer Nano ZS90 (Malvern, UK). Size and surface charge values are given as mean±S.D. of three independent measurements.

Protein concentration assay. The amount of proteins within the corona was determined by Bradford assay (Bio-rad) using bovine serum albumin at a known concentration as the standard to build a 5-point standard curve (R²=0.99). Protein concentrations are recorded as an average of three experiments ±S.D.

1D-SDS PAGE gels. Proteins in the corona were dissolved in in 8M Urea, 50 mM ammonium bicarbonate. An equal amount of Laemmli buffer 2×was added to the pellet and heated for 5 min at 90° C. before being loaded and resolved onto a 4-20% Mini-PROTEAN® TGX™ Precast Gels (Bio-Rad Laboratories, Hercules, CA) for 1 h at 120V. Proteins were stained with Coomassie Brilliant Blue (Fisher Scientific, Fair Lawn, NJ, USA) overnight followed by extensive washing in ultra-pure water.

Mass spectrometry/Statistics/PLS-DA. Mass spectrometry, statistical analysis and PLS-DA were performed as described in Example 1.

Example 6. A Multi-Nanoparticle Protein Corona Test for Detection of Alzheimer's Disease at Early Stage

The pathology of Alzheimer's disease begins decades before the detection of clinical symptoms. The need for accurate and noninvasive early diagnosis for Alzheimer's disease is rapidly growing. To address the issue, a state-of-the-art sensor array nanosystem was developed, which successfully detects minuscule changes in plasma protein patterns and uses clustering techniques to determine the presence of Alzheimer's disease. The developed technology can also be applied in the future to diagnose other diseases since the sensor array creates unique fingerprints for each plasma proteome change due to diseases and is sensitive enough to capture such changes unlike current technologies.

As discussed in the previous Examples, PCs' composition changes based on the plasma proteome that can be altered as a consequence of disease, which results in “personalized protein coronas” (PPCs). The PPCs, however, cannot provide a robust and precise strategy for early detection of diseases mainly due to the huge overlapping of the similar proteins in the protein corona composition. In this study, using the PPCs formed around a multi-NP platform containing six nanoparticles, we provided a fingerprint-patterns for robust and precise detection of AD with unprecedented prediction accuracy and specificity. The developed sensor array test successfully distinguished between patients with and without AD, as well as patients who developed AD several years afterwards (using cohort plasmas). This Examples provides a feasible, noninvasive alternative to current AD detection, allowing the ability to provide unparalleled early detection and treatment.

Results and Discussion

The sensor array test consists of incubating plasma samples with 6 different nanoparticles. The latter are 100 nm polystyrene and silica nanoparticles, each with tunable surface chemistries (plain, -amino and -carboxyl conjugated here after referred to as P, P—NH2, P—COOH, S, S—NH2, S—COOH) and narrow size distribution as described in Example 5 for CAD analysis. As initial proof-of-concept, to search for differences between AD and control plasmas, the size, surface charge and morphology of the nanoparticles before and after PC formation have been analyzed. Nanoparticle tracking analysis (Nanosight) has been applied to characterize the size of nanoparticles. During such analysis, a laser beam illuminates the nanoparticles, from which the scattered light is visualized through an optical microscope. Meanwhile, a video is recorded by a camera aligned to the beam showing the movement of the nanoparticles (30-60 frame/sec). Before incubation in plasma, all nanoparticles were homogeneous in size (FIG. 58 , polystyrene nanoparticles 90-100 nm; silica nanoparticles 80-100 nm) with a negative surface charge consistent with those provided by the manufacturer (Table 8). After 1 h incubation at 37° C. under agitation in plasma, PC-coated nanoparticles have been recovered by centrifugation followed by extensive washings to remove unbound and loosely attached proteins. In all cases, we revealed an increase in the size of PC-coated nanoparticles and a wider size distribution, which indicates a less homogeneous population (FIG. 54 , scatter plot). The average increase in size was 30 nm, thus indicating a 15-nm thickness of the PC layer, which is consistent with data reported in literature 1 and with what was observed using plasma from healthy volunteers (data not shown). The presence of plasma proteins on the nanoparticles' surface induced a change in their charge, which became less negative reaching the values typical of the plasma proteins (−20 mV to −0 mV to Table 8).

TABLE 8 zeta potentials of nanoparticles bare or after contacted with plasma Zeta Potentials Bare Healthy (mV) nanoparticles plasma AD plasma P −42.27 ± 0.54 −20.36 ± 1.54 −26.56 ± 2.14 P-NH2 −27.57 ± 1.63 −29.81 ± 1.55 −30.62 ± 0.74 P-COOH −49.38 ± 1.1 −34.87 ± 0.78 −27.02 ± 0.71 S −53.72 ± 1.05 −23.22 ± 1.55 −21.23 ± 0.54 S-NH2 −46.44 ± 0.86 −24.26 ± 0.95 −21.21 ± 0.38 S-COOH −56.77 ± 0.14 −28.37 ± 0.87 −25.69 ± 1.31

Slight differences in the surface charge of the same nanoparticle incubated with AD plasma and healthy plasma were observed (Table 8). However, those differences were not substantial and thus not useful in the discrimination between different plasma's conditions. Transmission electron microscopy (TEM) was also used to evaluate the morphology of nanoparticles, which remained unchanged after PC formation. Indeed, both before and after incubation with plasma, all nanoparticles had a round homogeneous shape (FIG. 55 ). The presence of a thin layer of proteins, associated to an increase in the size of PC-coated nanoparticles, confirming the results obtained by Nanosight, was observed (FIG. 55 ).

PCs associated with the particles were resolved by gel electrophoresis (SDS-PAGE) and later visualized by staining with Coomassie Brilliant Blue (FIG. 56 ). In general, by visually evaluating the lanes, the 6 nanoparticles had different PCs patterns, which was what expected and desired for the best performances of our approach. Silica nanoparticles seemed to adsorb less proteins on their surface than polystyrene nanoparticles. In most samples, the PC of plain polystyrene was more enriched than others in proteins at molecular weight ≈60 kD a, which are most likely attributable to Albumin. This was true both for AD patients' plasma and for control plasma (FIG. 56 , arrows). The densitometric analysis of bands associated to each PC confirmed that silica nanoparticles generally adsorbed lower amount of proteins, but revealed also that a higher number of proteins constitute their PCs: as for example, more than one band is present at level of Albumin for polystyrene nanoparticles' PC (FIG. 56 , arrows). On the other hand, several differences were recorded in the PPCs profiles of AD patients and healthy individual, particularly in the case of silica nanoparticles (FIG. 56 , arrows). However, those differences were not statistically significant and not sufficient to accurately discriminate between the two groups of patients under investigation. To deeper investigate the PCs and to know the exact identity and amount of proteins composing the different PCs, all the samples have been analyzed by mass spectrometry. Spectral-counting label free analysis, widely employed for quantitative profiling of the PCs around nanoparticles²⁻⁴, was used to determine the percentage contribution of each protein in the PCs. This calculation was done six times for each plasma patient (incubated separately with each nanoparticle), thus allowing the formation of an AD-specific PC profile derived from the combination of the contribution of the PCs related to six nanoparticles. Table 9 (See FIG. 68 ) describes the patient population used.

CONCLUSION

This work represents a proof-of-concept study for the development of a MNPC blood test for the diagnosis of AD. The MNPC test showed unprecedented prediction accuracy and specificity. While individual biomarkers blood-based tests are often associated with false positive and thus require further analyses to confirm the diagnosis, our approach records the interactions of all the high-affinity proteins with the set of 6 nanoparticles, thus allowing the creation of a high-specificity PC fingerprint of a given disease. The nanoparticles act as nano-concentrator of plasma proteins on their surface (each nanoparticle concentrates the plasma proteins with higher affinity towards its surface): this helps in the revelation of proteins whose levels only change slightly in pathological conditions with respect to a healthy status. These little changes may belong both to high abundance and low abundance plasma proteins. In this study, we reported a relatively small number of patients because each patient's plasma was analyzed 6 times using different nanoparticles, and so the results obtained for each patient are 6 times more specific than those obtained when a single analysis is performed.

Materials and Methods

Nanoparticles. Silica particles (plain, amino and carboxyl-conjugated) were purchased by Kisker-Products (see website at kisker-biotech.com). Polystyrene particles (plain, amino and carboxyl-conjugated) were purchased by Polyscience, Inc. (see website at polysciences.com). According to manufacturer's all the particles had the same size (90-100 nm). Their morphology, average size and zeta potential were characterized as described later in this section.

Personalized Protein Corona Formation.

The PCs were created by incubating 0.5 mg of nanoparticles in deionized H₂O with the same volume of human plasma. Incubation was performed in 37° C. under agitation for 1 h. Immediately after incubation, PC-coated nanoparticles have been recovered by centrifugation (14,000 rpm and 10° C. for 30 minutes) and extensive washing in cold phosphate-buffered saline (PBS) to remove unbound or weakly bound proteins. The pellet of PC-coated nanoparticles was resuspended in 8M Urea, 50 mM ammonium bicarbonate for SDS-PAGE gels and LC/MSMS analysis or in deionized H₂O for dynamic light scattering and ζ-potential analyses.

Physicochemical characterization of nanoparticles. Size was measured by Nanoparticle tracking analysis (Nanosight, Malvern, UK). The software calculates the size according to ζ-potential of bare and PC-coated nanoparticles has been determined using a Zetasizer Nano ZS90 (Malvern). nanoparticles were diluted in water before the analysis to a concentration of 50 ng/ml. Size and surface charge values are given as mean±S.D. of three independent measurements. For transmission electron microscopy (TEM) analysis, samples and grids have been labeled with 1% uranyl acetate. Tecnai G2 Spirit BioTWIN Transmission Electron Microscope equipped with an AMT 2k CCD camera was used.

One-dimensional gel electrophoresis. Personalized protein coronas were dissolved in 8M Urea, 50 mM ammonium bicarbonate. An equal amount of Laemmli buffer 2×was added to the pellet and heated for 5 min at 90° C. before being loaded and resolved onto a 4-20% Mini-PROTEAN® TGX™ Precast Gels (Bio-Rad Laboratories, Hercules, CA) for 1 h at 120V. Proteins were stained with Coomassie Brilliant Blue (Fisher Scientific, Fair Lawn, NJ, USA) overnight followed by extensive washing in ultra-pure water. Densitometric analysis of the band intensities have been performed by ImageJ (website: imagej.nih.gov/ij/).

Protein identification and quantification by mass spectrometry. Proteins were reduced with 10 mM dithiothreitol (Sigma) for 1 h at 56° C. and then alkylated with iodoacetamide (Sigma-Aldrich, St Loius, MO, USA) for 1 h at 25° C. in the dark. Proteins were then digested with modified trypsin (Promega, Madison, WI, USA) at an enzyme/substrate ratio of 1:50 in 100 mM ammonium acetate, pH 8.9 at 25° C. overnight. Trypsin activity was halted by addition of acetic acid (99.9%, Sigma-Aldrich) to a final concentration of 5%. Peptides were desalted using C18 SpinTips (Protea, Morgantown, WV) then vacuum centrifuged and stored at −80° C. until the day of the analysis. Peptides were separated by reverse phase HPLC (Thermo Fisher, Waltham, MA Easy nLC1000) using a precolumn (made in house, 6 cm of 10 μm C18) and a self-pack 5 μm tip analytical column (12 cm of 5 μm C18, New Objective) over a 140-minute gradient before nanoelectrospray using a QExactive mass spectrometer (Thermo Fisher). Solvent A was 0.1% formic acid and solvent B was 80% MeCN/0.1% formic acid. The gradient conditions were 2-10% B (0-3 min), 10-30% B (3-107 min), 30-40% B (107-121 min), 40-60% B (121-126 min), 60-100% B (126-127 min), 100% B (127-137 min), 100-0% B (137-138 min), 0% B (138-140 min), and the mass spectrometer was operated in a data-dependent mode. The parameters for the full scan MS were: resolution of 70,000 across 350-2000 m/z, AGC 3e6, and maximum IT 50 ms. The full MS scan was followed by MS/MS for the top 10 precursor ions in each cycle with a NCE of 28 and dynamic exclusion of 30 s. Raw mass spectral data files (.raw) were searched using Proteome Discoverer (Thermo Fisher) and Mascot version 2.4.1 (Matrix Science). Mascot search parameters were: 10 ppm mass tolerance for precursor ions; 15 millimass units (mmu) for fragment ion mass tolerance; 2 missed cleavages of trypsin; fixed modification was carbamidomethylation of cysteine; variable modifications were methionine oxidation. Only peptides with a Mascot score 25 were included in the data analysis. Spectral counting was performed by summing the total number of peptides selected for fragmentation each protein.

Example 7. Size of Particles Effects Amount of Protein Bound

This Example demonstrates that the use of different size nanoparticles made of the same material provide a different biomolecule fingerprint for each size. Silica nanoparticles of three different diameters (100 nm (0.1 μm), 3 μm and 4 μm) were incubated with the same plasma sample. The beads where analyzed by SDS-PAGE. As demonstrated in FIG. 58 , the larger the beads, the more proteins are comprised within the biomolecule signature. Further, each bead size has a distinct biomolecule corona signature and thus the combination of different sizes of nanoparticle alone allow for the development of a distinct biomolecule fingerprint. As shown, there are distinct differences in the pattern or proteins between the three different sized beads.

A sensor array can be made using nanoparticles of different sizes which each will give a different biomolecule fingerprint.

Example 8. Sensor Array can Provide a Biomolecule Fingerprint Comprising Nucleic Acids

The sensor array and associated biomolecule corona signature along with proteins contains nucleic acids that make up the biomolecule corona. This Example demonstrates the composition of nucleic acids that bind to silica nanoparticles with neutral surface nanoparticles. Nanoparticles were incubated with plasma, and the associated nucleic acids were analyzed (FIG. 59 ). FIGS. 60 and 61 depict the analysis of nucleic acid in all samples and its content in plasma, (nucleic acid amount in plasma was 33.8 pg/μl). The nucleic acid content of the biomolecule coronas associated with the nanoparticle was analyzed. The proteins were either dissociated from nanoparticle using urea and the nucleic acids subsequently analyzed (FIG. 62 , nucleic acid amount 14.0) or the proteins were not dissociated from the corona and the nucleic acids analyzed (FIG. 63 , 14.4 pg/μl). Alternatively, the nanoparticles can be incubated with nucleic acids that have been purified from the plasma with a plasma kit and then incubated with the bare particles (FIG. 64 , nucleic acid amount 13.2 pg/μl).

The outcomes revealed the capacity of nanoparticles in adsorption of nucleic acid in the biomolecular corona composition. 

1-29. (canceled)
 30. A method for assaying a biological sample, comprising: measuring protein coronas formed from contacting particles with a biological sample wherein a subset of proteins in the biological sample are detected with an instrument to measure the subset of the proteins across a dynamic range of more than 6 orders of magnitude in the biological sample by: (a) contacting the particles with the biological sample that comprises the subset of the proteins to allow the protein coronas to form on surfaces of the particles; (b) separating the particles comprising the protein coronas from the biological sample by isolating the particles from the biological sample, thereby separating the subset of the proteins from the biological sample; (c) preparing the protein coronas for detecting the proteins; and (d) detecting the proteins.
 31. The method of claim 30, wherein the particles comprise silica.
 32. The method of claim 31, wherein the particles comprise carboxylate or carboxylic acid surface modifications.
 33. The method of claim 32, wherein the particles comprise iron oxide.
 34. The method of claim 33, wherein the particles comprise microparticles.
 35. The method of claim 34, wherein the particles comprise a negative surface charge.
 36. The method of claim 33, wherein the contacting is performed to obtain the protein coronas on the particles in the same biological sample at about the same time.
 37. The method of claim 33, wherein the contacting is performed at a temperature between 10° C. and 40° C. for 15 to 60 minutes.
 38. The method of claim 37, wherein the preparing comprises reducing and alkylating the proteins.
 39. The method of claim 38, wherein the preparing comprises digesting the proteins to produce digested peptides.
 40. The method of claim 39, wherein the detecting the proteins comprises detecting the digested peptides.
 41. The method of claim 40, wherein the biological sample comprises plasma or serum.
 42. The method of claim 41, wherein the biological sample comprises plasma.
 43. The method of claim 42, wherein the contacting concentrates a first protein that comprises less than 100 ng/mg in the biological sample.
 44. The method of claim 43, wherein the contacting concentrates a second protein that comprises less than 10 ng/mg in the biological sample.
 45. The method of claim 44, wherein the contacting concentrates a third protein that is present in a sub-nanogram range in the biological sample.
 46. The method of claim 45, wherein the detecting comprises detecting the first protein, the second protein, and the third protein.
 47. The method of claim 39, wherein the preparing comprises purifying the digested peptides using solid phase extraction.
 48. The method of claim 30, wherein the detecting comprises performing mass spectrometry.
 49. The method of claim 48, wherein the mass spectrometry comprises LC-MS/MS.
 50. The method of claim 30, wherein a dynamic range limitation of the instrument is 4-6 orders of magnitude.
 51. The method of claim 30, wherein the particles comprise polyethylene imine, microparticles, ammonium group functionalizations, or ammonium group functionalizations with a positive surface charge.
 52. The method of claim 30, wherein the particles vary in sizes including from about 1000 nm to about 5000 nm.
 53. The method of claim 30, wherein the particles vary in sizes including from about 1000 nm to about 10000 nm.
 54. The method of claim 30, wherein the particles comprise a first particle that is no more than about 3 μm and a second particle that is at least about 4 μm.
 55. The method of claim 30, wherein proteins across a dynamic range of ten orders of magnitude are detected using mass spectrometry. 